Method and Systems for Measuring Neural Activity

ABSTRACT

Provided herein is a method of optically recording neural activity in one or more regions of a target tissue. Also provided is a method of optically modulating the activity of a neural tissue. Further provided is a system that finds use in performing the present methods.

CROSS-REFERENCE

This application claims the benefit of U.S. Provisional Patent Application No. 62/257,140, filed Nov. 18, 2015, which application is incorporated herein by reference in its entirety.

INTRODUCTION

Genetically-encoded Ca²⁺ indicators (GECIs) are polypeptides whose fluorescence is modulated by intracellular concentration of calcium ions. GECIs are used to optically measure neuronal activity at single resolution and to study in vivo dynamics and population coding under a microscope system.

Optogenetic refers to methods of manipulating the activity of excitable cells, such as neurons, by altering the membrane potential of excitable cells expressing light-activated proteins that depolarize or hyperpolarize cells in response to light.

Optical fibers, which bi-directionally transmit light between separate sites, can be used for optical imaging and/or manipulating neural activity relevant to behavioral circuitry mechanisms.

SUMMARY

Provided herein is a method including a) illuminating one or more regions of a target tissue with a light stimulus comprising light pulses of a plurality of wavelengths, wherein each of the one or more regions comprises one or more collections of a plurality of neurons, or a subcellular portion thereof, labeled with one or more neural activity-dependent fluorescent moieties; the light pulses comprise: i) a first set of light pulses at a first wavelength; and ii) a second set light pulses at one or more wavelengths, wherein each of the one or more wavelengths are different from the first wavelength and are at an excitation wavelength of the one or more neural activity-dependent fluorescent moieties, and wherein each light pulse of the first set are interleaved among light pulses of the second set, thereby generating fluorescence from each of the one or more regions, wherein a multimode optical fiber is configured to direct the light stimulus to, and collect the fluorescence from, each of the one or more regions; b) recording, onto independent frames of an image detector for each light pulse, an image of a cross-section of the multimode optical fiber for each of the one or more regions, wherein a cross-sectional average of the fluorescence generated in response to the second set of light pulses is representative of an aggregate neural activity of the one or more regions; and c) analyzing the recorded image, to generate an output comprising a measure of the aggregate neural activity in each of the one or more regions. In some embodiments, the multimode optical fiber has a diameter in the range of 100 to 1000 μm. In some embodiments, the one or more collections include one or more functionally-defined collections of a plurality of neurons.

In any embodiment, the one or more regions may include: a first collection of a plurality of neurons, each neuron of the first collection containing a first neural activity-dependent fluorescent moiety; and a second collection of a plurality of neurons, each neuron of the second collection containing a second neural activity-dependent fluorescent moiety, and wherein the second set of light pulses include: a third set of light pulses at a second wavelength, different from the first wavelength, wherein the second wavelength is at an excitation wavelength of the first neural activity-dependent fluorescent moiety; and a fourth set of light pulses at a third wavelength, different from the first and second wavelengths, wherein the third wavelength is at an excitation wavelength of the second neural activity-dependent fluorescent moiety, and wherein the recording includes recording a first image and a second image of the terminal cross-section of the multimode optical fiber from each of the one or more regions, wherein a cross-sectional average of the fluorescence generated in response to the third set of light pulses in the first image is representative of an aggregate neural activity of the first collection of a plurality of neurons, and a cross-sectional average of the fluorescence generated in response to the fourth set of light pulses in the second image is representative of an aggregate neural activity of the second collection of a plurality of neurons. In some cases, the first collection and the second collection are distinct collections of a plurality of neurons. In some cases, the first collection and the second collection are non-overlapping collections of a plurality of neurons. In some embodiments, the light pulses of the third set and light pulses of the fourth set are synchronous.

In any embodiment, the light stimulus may include an alternating order of a light pulse from the first set of light pulses and one or more light pulses from the second set of light pulses.

In any embodiment, the analyzing may include: 1) demarcating the cross-section of the multimode optical fiber from each of the one or more regions in the recorded image; and 2) calculating an average of the fluorescence across each of the cross-sections.

In any embodiment, the analyzing may include 3) calculating a normalized change in the fluorescence over a baseline fluorescence for each cross-section of the multimode optical fibers in the recorded image. In some cases, the baseline fluorescence is a median of the average fluorescence within each cross-section of the multimode optical fibers across a plurality of recorded images.

In any embodiment, a neural activity-independent fluorescence may be generated in response to the first set of light pulses. In some embodiments, the first wavelength is at an isosbestic point of at least one of the one or more neural activity-dependent fluorescent moieties. In some cases, the analyzing includes 4) subtracting an average of the neural activity-independent fluorescence across a cross-section from an average of the neural activity-dependent fluorescence across the cross-section, to obtain a motion-corrected measure of the aggregate neural activity.

In any embodiment, at least one of the one or more regions includes a third collection of a plurality of neurons, or a subcellular portion thereof, each neuron of the third collection containing a light-activated polypeptide configured to modulate the electrical activity of the neuron in response to the light stimulus, wherein the first wavelength is at an activation wavelength of the light-activated polypeptide. In some embodiments, the third collection comprises a functionally-defined collection of a plurality of neurons. In some cases, the third collection includes the same neurons as at least one of the one or more collections of a plurality of neurons. In some embodiments, the light pulses of the second set have a power of 50 μW or less. In some embodiments, light pulses in the first set are pulsed at a first frequency less than a second frequency at which light pulses of the second set are pulsed. In some embodiments, the light pulses of the first set have a power sufficient to approximate neural activity-dependent fluorescence generated by a natural stimulus. In some embodiments, the light-activated polypeptide is a depolarizing or hyperpolarizing light-activated polypeptide. In some embodiments, the light-activated polypeptide is an ion channel or an ion pump. In some cases, the light-activated polypeptide is selected from: ChR2, iC1C2, C1C2, GtACR2, NpHR, eNpHR3.0, C1V1, VChR1, VChR2, SwiChR, Arch, ArchT, KR2, ReaChR, ChiEF, Chronos, ChRGR, CsChrimson, bReaCh-ES, and variants thereof.

In any embodiment, the target tissue may be an in vivo tissue. In some embodiments, the target tissue is in a freely moving animal.

In any embodiment, the method may include illuminating two or more regions of the target tissue. In some cases, the two or more regions include functionally distinct regions of the target tissue. In some embodiments, the two or more regions comprise anatomically distinct regions of the target tissue. In some embodiments, the two or more regions comprise functionally connected regions of the target tissue.

In any embodiment, the one or more regions may include one or more mammalian brain regions. In some cases, the one or more mammalian brain regions is selected from at least a portion of the ventral tegmental area (VTA), prefontal cortex (PFC), nucleus accumbens (NAc), amygdala (BLA), substantia nigra, ventral pallidum, globus pallidus, dorsal striatum, ventral striatum, subthalamic nucleus, hippocampus, dentate gyrus, cingulate gyrus, entorhinal cortex, olfactory cortex, sensory cortex, thalamus, primary motor cortex, and cerebellum.

In any embodiment, one or more regions may include neuronal projections of the one or more collections of a plurality of neurons. In some cases, the neuronal projections are axonal projections.

In any embodiment, the one or more neural activity-dependent fluorescent moieties may include a genetically-encoded indicator dye.

In any embodiment, the one or more collections may include a plurality of dopaminergic, cholinergic, GABAergic, glutamatergic, or peptidergic neurons.

In any embodiment, the one or more neural activity-dependent fluorescent moieties may include a calcium- and/or a voltage-sensitive indicator dye.

In any embodiment, the one or more collections may include genetically modified neurons expressing the one or more activity-dependent fluorescent moieties. In some cases, expression of each of the one or more neural activity-dependent fluorescent moieties is regulated under a cell-specific promoter. In some cases, expression of each of the one or more neural activity-dependent fluorescent moieties is regulated in a Cre-dependent manner. In some embodiments, the method further includes, before the illuminating, genetically modifying neurons of the one or more regions of the target tissue to express the one or more neural activity-dependent fluorescent moieties.

In any embodiment, the image detector may be a charge-coupled device (CCD) or a complementary metal oxide semiconductor (CMOS) camera.

In any embodiment, the recording may include recording the image synchronously with the second set of light pulses.

In any embodiment, the recording comprises recording the image synchronously with the first set and second set of light pulses.

Also provided herein is a system that includes a) an illumination unit; b) an objective, wherein the objective is configured to receive light from the illumination unit and to focus the light at a working distance from the objective; c) a plurality of light conduits, each light conduit containing one or more multimode optical fibers and defining a first end, a second end opposite the first, and a light conduit numerical aperture, wherein a terminus at the first end of each of the light conduits is at the working distance from the objective; a terminal cross-section of a multimode optical fiber at the first end of each of the light conduits is in a field of view of the objective; and the light conduit numerical aperture is less than a numerical aperture of the objective; and d) an image detector; wherein the system is configured to: generate a light stimulus including light pulses of a plurality of wavelengths; illuminate a region in a target tissue at the second end of each of the plurality of light conduits, the region containing one or more collections of a plurality of neurons, or a subcellular portion thereof, labeled with one or more neural activity-dependent fluorescent moieties, wherein the plurality of wavelengths comprises one or more wavelengths at an excitation wavelength of the one or more neural activity-dependent fluorescent moieties; collect fluorescence from the region at the second end of the same light conduit of the plurality of light conduits used to illuminate the region; and record an image including all of the terminal cross-sections of the multimode optical fibers at the first end of the light conduits onto a frame of the image detector. In some embodiments, the one or more multimode optical fibers have a diameter in the range of 100 to 1000 μm. In some embodiments, the numerical aperture of the multimode optical fiber is 0.30 or greater. In some embodiments, the second end is configured to be implanted in the target tissue.

In any embodiment, each of the light conduits may include: an implantable fiber-optic element including an attachment element; and one or more multimode optical fibers configured to attach to the attachment element.

In any embodiment, the plurality of wavelengths may include a wavelength at an isosbestic point of the one or more neural activity-dependent fluorescent moieties.

In any embodiment, the plurality of wavelengths may include a plurality of wavelengths at an excitation wavelength of a plurality of neural activity-dependent fluorescent moieties.

In any embodiment, the plurality of wavelengths may include one or more wavelengths at an activation wavelength of one or more light-activated polypeptides.

In any embodiment, the light source may be a light-emitting diode (LED) or a laser.

In any embodiment, the image detector may be a charge-coupled device (CCD) or a complementary metal oxide semiconductor (CMOS) camera.

In any embodiment, the system further may include an image splitter positioned in front of the image detector.

In any embodiment, the system may further include: e) a processor; and f) a computer-readable medium containing instructions that, when executed by the processor, causes the system to: generate a light stimulus containing i) a first set of light pulses at a first wavelength; and ii) a second set of light pulses at one or more wavelengths, each of the one or more wavelengths different from the first wavelength, using the illumination unit, wherein the one or more wavelengths are each at the excitation wavelength of the one or more neural activity-dependent fluorescent moieties, and wherein each light pulse of the first set are interleaved among light pulses of the second set, thereby generate fluorescence from each of the one or more regions; and record the image onto independent frames of the image detector per each light pulse. In some cases, the one or more wavelengths include two or more wavelengths.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-1H are a collection of diagrams and graphs showing simultaneous calcium measurements from multiple deep brain regions using an sCMOS camera, according to embodiments of the present disclosure.

FIGS. 2A-2H are a collection of diagrams and graphs showing dual-color imaging of different populations and simultaneous recording and perturbation of neural activity according to embodiments of the present disclosure.

FIGS. 3A-3C are a collection of diagrams and graphs showing synchronous camera and photoreceiver measurements of reward-related photometry signals in the VTA, according to embodiments of the present disclosure.

FIGS. 4A-4F are a collection of images and graphs showing GECI fluorescence emission to calcium-dependent excitation wavelengths and to a calcium-independent isosbestic wavelength, according to embodiments of the present disclosure.

FIG. 5 is a collection of graphs showing an example of correcting motion-related artifacts present in the 410 nm isosbestic wavelength, according to embodiments of the present disclosure.

FIGS. 6A-6C are a collection of graphs showing example traces of simultaneous 4-fiber recordings of VTA-DA cell bodies and projections during reward and tail shock, according to embodiments of the present disclosure.

FIGS. 7A-7D are a collection of images showing confirmation of fiber location and virus expression for 4-fiber surgeries, according to embodiments of the present disclosure.

FIGS. 8A and 8B are a collection of diagrams showing microscope configurations used for dual-color imaging and simultaneous imaging and perturbation experiments, according to embodiments of the present disclosure.

FIGS. 9A and 9B are a collection of images showing confirmation of fiber location and virus specificity for dual-color imaging, according to embodiments of the present disclosure.

FIGS. 10A-10F are a collection of graphs showing the characterization of a bReaCh-ES opsin, according to embodiments of the present disclosure.

FIGS. 11A-11D are a collection of graphs showing control experimental results for simultaneous imaging and perturbation experiment, according to embodiments of the present disclosure.

FIG. 12A-12F provide amino acid sequences of ReaChR and bReachES polypeptides.

FIG. 13A-13S provide amino acid sequences of single-fluorescent protein genetically encoded calcium indicators.

FIG. 14A-14C provide amino acid sequences of multi-fluorescent protein genetically encoded calcium indicators.

FIG. 15A-15U provide amino acid sequences of various light-responsive polypeptides.

DEFINITIONS

The terms “polypeptide”, “peptide” and “protein” are used interchangeably herein to refer to polymers of amino acids of any length. The polymer may be linear, it may comprise modified amino acids, and it may be interrupted by non-amino acids. The terms also encompass an amino acid polymer that has been modified; for example, disulfide bond formation, glycosylation, lipidation, acetylation, phosphorylation, or any other manipulation, such as conjugation with a labeling component. As used herein the term “amino acid” refers to either natural and/or unnatural or synthetic amino acids, including glycine and both the D or L optical isomers, and amino acid analogs and peptidomimetics.

The term “genetic modification” refers to a permanent or transient genetic change induced in a cell following introduction into the cell of a heterologous nucleic acid (e.g., a nucleic acid exogenous to the cell). Genetic change (“modification”) can be accomplished by incorporation of the heterologous nucleic acid into the genome of the host cell, or by transient or stable maintenance of the heterologous nucleic acid as an extrachromosomal element. Where the cell is a eukaryotic cell, a permanent genetic change can be achieved by introduction of the nucleic acid into the genome of the cell. Suitable methods of genetic modification include viral infection, transfection, conjugation, protoplast fusion, electroporation, particle gun technology, calcium phosphate precipitation, direct microinjection, and the like.

A “plurality” contains at least 2 members. In certain cases, a plurality may have at least 10, at least 100, at least 1000, at least 10,000, at least 100,000, at least 10⁶, at least 10⁷, at least 10⁸ or at least 10⁹ or more members.

“Substantially” as used herein, may be applied to modify any quantitative representation that could permissibly vary without resulting in a change in the basic function to which it is related.

“Representative” as used herein, may be used to indicate that a variation in an underlying phenomenon is related to a quantity, e.g., a measured quantity by an experimentally-defined relationship.

“Cellular electrical activity” as used herein, refers to activity of cells that are related to changes in the concentration of ionic species (e.g., sodium ions, potassium ions, calcium ions, etc.) within the cell. Electrical activity may include changes in the intracellular concentration of ions, such as calcium ions caused by, e.g., opening or closing of ion channels in the plasma membrane, endoplasmic reticulum; activation or inactivation of ion pumps or transporters; etc. Electrical activity may include changes in membrane potential caused by changes in the concentration gradient of ionic species across the plasma membrane. Cellular electrical activity may include neural activity, i.e., cellular electrical activity of a neuron or a collection of neurons.

“Interleaved” as used herein, may be used to describe a relationship between a first event and two second events, where the first event occurs in between the two second events, and where the first event does not overlap with either of the two second events. In some cases, any two consecutive events may occur substantially immediately one after another.

A “wavelength” as used herein, may include a band of wavelength values centered on a specific wavelength value. The width of the band of wavelength values may vary and may depend on the desired and/or practical level of differentiation between different excitation and emission lights used in the present optical method and system.

“Excitation wavelength” as used in reference to a neural-activity dependent fluorescent moiety, refers to the wavelength by which the fluorescent moiety is excited generates an emission that is representative of neural activity. In some cases, the excitation wavelength is the optimal wavelength at which neural-activity dependent fluorescence is emitted by the fluorescent moiety.

“Isosbestic point” as used herein, may refer to a wavelength at which the total absorbance (i.e., fluorescence) of a neural-activity dependent fluorescent moiety does not change regardless of the electrophysiological state of the cellular milieu. Thus, a calcium indicator in a neuron stimulated by light having a wavelength substantially at the isosbestic point of the calcium indicator will emit the same intensity of fluorescence regardless of the concentration of calcium in the neuron, within the physiological range.

“Working distance” as used herein, refers to the distance between the front edge of the objective lens (e.g. the surface of the front lens closest to the sample being observed in a typical light microscope setup) and the surface of the sample being observed (i.e. the surface of the cover glass) when the observed sample is in focus. Working distance may also indicate the location in front of the objective where a sample would be in focus.

“Terminus” as used in reference to an optical fiber, refers to an end where light enters or exits the optical fiber.

“Cross-section” as used in reference to an optical fiber, refers to an area defined by an intersection between the optical fiber and a plane substantially perpendicular to the direction of travel of bulk light through the optical fiber.

An “image detector,” as used herein, refers to an optical detection and/or recording device that measures light intensity across individual pixels of an optical sensor, where the spatial distribution of the individual pixels corresponds to a spatial distribution of the source of the light. Thus, an image detector may simultaneously capture the spatial distribution of light intensities in a light pattern emitted from a sample.

“Frame” as used herein, may refer to a single two-dimensional image captured by exposing the image sensor of an image detector to light collected onto the image sensor for a desired amount of time.

“Aggregate” as used herein, may be used to indicate a property or characteristic of a population without regard to the individual contributions to the property or characteristic. Thus, an aggregate neural activity may indicate the neural activity of a population of neurons without providing any underlying information about the activity of any one of the individual neurons in the population, except in the case where the population is a single neuron.

“Synchronous” as used herein, may be applied to any two or more sequences of events that occur with a temporal pattern that is substantially the same. Events in the two or more sequences that are synchronous may start at substantially the same times, may have a midpoint within events that are at substantially the same times, and/or end at substantially the same times. “Simultaneous” may indicate two events that are synchronous and substantially coextensive in duration.

Before the present disclosure is further described, it is to be understood that the disclosed subject matter is not limited to particular embodiments described, as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting, since the scope of the present disclosure will be limited only by the appended claims.

Where a range of values is provided, it is understood that each intervening value, to the tenth of the unit of the lower limit unless the context clearly dictates otherwise, between the upper and lower limit of that range and any other stated or intervening value in that stated range, is encompassed within the disclosed subject matter. The upper and lower limits of these smaller ranges may independently be included in the smaller ranges, and are also encompassed within the disclosed subject matter, subject to any specifically excluded limit in the stated range. Where the stated range includes one or both of the limits, ranges excluding either or both of those included limits are also included in the disclosed subject matter.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the disclosed subject matter belongs. Although any methods and materials similar or equivalent to those described herein can also be used in the practice or testing of the disclosed subject matter, the preferred methods and materials are now described. All publications mentioned herein are incorporated herein by reference to disclose and describe the methods and/or materials in connection with which the publications are cited.

It must be noted that as used herein and in the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, reference to “an image” includes a plurality of such images and reference to “the region of a target tissue” includes reference to one or more regions of a target tissue and equivalents thereof known to those skilled in the art, and so forth. It is further noted that the claims may be drafted to exclude any optional element. As such, this statement is intended to serve as antecedent basis for use of such exclusive terminology as “solely,” “only” and the like in connection with the recitation of claim elements, or use of a “negative” limitation.

It is appreciated that certain features of the disclosed subject matter, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment. Conversely, various features of the disclosed subject matter, which are, for brevity, described in the context of a single embodiment, may also be provided separately or in any suitable sub-combination. All combinations of the embodiments pertaining to the disclosure are specifically embraced by the disclosed subject matter and are disclosed herein just as if each and every combination was individually and explicitly disclosed. In addition, all sub-combinations of the various embodiments and elements thereof are also specifically embraced by the present disclosure and are disclosed herein just as if each and every such sub-combination was individually and explicitly disclosed herein.

The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the disclosed subject matter is not entitled to antedate such publication by virtue of prior invention. Further, the dates of publication provided may be different from the actual publication dates which may need to be independently confirmed.

DETAILED DESCRIPTION

As summarized above, methods and systems optically recording cellular electrical activity, e.g., intracellular calcium dynamics, in one or more regions of a target tissue are provided. The present methods and systems provide for rapid, simultaneous optical recording of cellular electrical activity-dependent fluorescence emitted by a collection of electrically excitable cells, e.g., neurons, that are labeled with a cellular electrical activity-dependent fluorescent moiety in one or more regions of a target tissue. The simultaneous recording may be scaled to a number of regions within a target tissue, such that the cellular electrical activity-dependent fluorescence emitted by a collection of electrically excitable cells in two or more regions may be recorded simultaneously. In some embodiments, the present methods and systems provide for simultaneous recording of cellular electrical activity-dependent fluorescence emitted by a plurality of collections of electrically excitable cells in a region, using a plurality of cellular electrical activity-dependent fluorescent moieties. In some embodiments, the present methods and systems provide for optically modulating the electrical activity of cells that contain a light-activated polypeptide in conjunction with recording electrical activity. Further aspects of the present methods and systems are now described in detail.

Systems

A system of the present disclosure may be described with reference to the accompanying figures. However, it is noted that the figures may show an example of the specific components of an embodiments of the present system, and that other embodiments of the present system is envisioned to be within the scope of this disclosure, by substituting the specific components with equivalent structural and/or equivalent functional components known in the art.

A system of the present disclosure includes an illumination unit, including one or more light sources, e.g., a light-emitting diode (LED) and/or a laser light source, that may be configured to emit light at a suitable wavelength (FIGS. 1A, 8A and 8B). Having multiple light sources can allow the user to control the illumination pattern, e.g., the timing of light pulses, for each light source independently of each other. The illumination unit may also include any other suitable optical components to direct, focus and otherwise control the light being generated by the light source. Suitable optical components include, but are not limited to, lenses, tube lenses, collimators, dichroic mirrors, filters, shutters, etc. Thus, the illumination unit may be configured to project a light stimulus that includes light pulses of a number of wavelengths. A controller may be in communication with the illumination unit so as to control the timing, duration, and/or wavelength of the light pulse generated by the illumination unit.

The present system may also include an objective placed in the optical path of the system so as to focus light from the illumination unit at the working distance of the objective. In front of the object, a bundle of optical fibers, e.g., multimode optical fibers, is positioned such that the terminal cross-sections of some or all of the optical fibers are focused and in the field of view of the objective (FIG. 1A, top right inset). The numerical aperture of the optical fiber can be less than the numerical aperture of the objective. The bundle of optical fibers may be part of a multi-fiber branching patchcord that terminates in a number of separate optic fiber branches. The ends of the optic fiber branches may be equipped with a ferrule, e.g., a stainless steel ferrule, to allow attachment to optic fibers that are implanted in a tissue, e.g., implanted to position the fiber ends in different regions of a brain in a subject, such as a mouse or rat (see FIGS. 1B, 1F, 2A and 2E). Thus, the light stimulus generated by the light sources and projected to the back of the objective through the optical light path can be directed into the optical fibers and simultaneously illuminate multiple, distinct regions of the brain where the branched optic fiber ends are implanted.

The same optical fibers used to deliver the light stimulus to the target regions of a tissue are also configured to collect fluorescence that is emitted from the target areas. Thus, the target regions may contain a population of neurons that are genetically modified to express a neural activity-dependent fluorescent moiety, such as a genetically encoded calcium indicator. When a target region is stimulated with a light stimulus having a wavelength at or around the excitation wavelength of the neural activity-dependent fluorescent moiety, the illuminated neurons may emit fluorescence that is representative of the level of neural activity in the region. The fluorescence from an individual neuron may be representative of the activity level of the individual neuron. The fluorescence collected from two or more neurons may be representative of the average activity level of the neurons. By “average” is meant the arithmetic mean.

The fluorescence emitted from the target tissue and collected by the optical fibers is directed back to and collected by the objective, and further directed to an image sensor of an image detector, e.g. a digital camera. The optical path of the collected fluorescence may include any suitable components, such as a dichroic mirror and lenses, to form an image of the terminal cross-sections of the optical fibers onto the image sensor and capture the image with the image detector. In some cases, an image splitter may be positioned in the light path before, e.g., in front of, the image detector (FIG. 8A). In such cases, an appropriate configuration of the image splitter can divide the fluorescence emitted from the tissue based on the wavelength and separate images for different wavelengths of fluorescence may be captured by the image detector simultaneously.

The light source of a system of the present disclosure may include any suitable light source. In some cases, the light source is an LED, an LED array or a laser. The light source may emit light having a wavelength in the infrared range, near-infrared range, visible range, and/or ultra-violet range. The light source may emit a light at a wavelength around 350 nm or more, e.g., around 380 nm or more, around 410 nm or more, around 440 nm or more, around 470 nm or more, around 500 nm or more, around 560 nm or more, around 594 nm or more, around 600 nm or more, around 620 nm or more, around 650 nm or more, around 680 nm or more, around 700 nm or more, around 750 nm or more, around 800 nm or more, including around 900 nm or more, and may emit a light at a wavelength around 2,000 nm or less, e.g., around 1,500 nm or less, 1,000 nm or less, 800 nm or less, 700 nm or less, 650 nm or less, including 620 nm or less, or 600 nm or less. In some cases, the light source may emit a light at a wavelength in the range of about 350 nm to about 2,000 nm, e.g., about 410 nm to about 2,000 nm, about 440 nm to about 1,000 nm, about 440 nm to about 800 nm, including about 440 nm to about 620 nm. The light source may be configured to produce a continuous wave, a quasi-continuous wave, or a pulsed wave light beam. In certain embodiments, a laser light source is a gas laser, solid state laser, a dye laser, semiconductor laser (e.g., a diode laser), or a fiber laser.

The number of wavelengths produced by the light source may be any suitable number of wavelengths. In some cases, the light source produces light with 1 or more, e.g., 2 or more, 3 or more, including 4 or more, or 5 or more, or 6 or more, or 7 or more, or 8 or more, or 9 or more, or 10 or more, distinct wavelengths of light, and produces light with 10 or fewer, e.g., 9 or fewer, 8 or fewer, 7 or less, 6 or fewer, including 5 or fewer distinct wavelengths of light. In some embodiments, the light source produces light in the range of 1 to 10, e.g., 1 to 8, 2 to 6, 2 to 5, including 2 to 4 distinct wavelengths.

The objective may be any suitable objective for use in the present system. The objective may be an air objective, oil objective, water objective, a water and air objective, etc. The objective may have any suitable numerical aperture for use in the present system. In some cases, the objective has a numerical aperture of 0.3 or more, e.g., 0.4 or more, 0.5 or more, including 0.6 or more, and has a numerical aperture of 1.6 or less, e.g., 1.4 or less, 1.2 or less, 1.0 or less, 0.9 or less, including 0.8 or less. In some cases, the objective has a numerical aperture in the range of 0.3 to 1.6, e.g., 0.3 to 1.4, 0.4 to 1.2, 0.5 to 1.0, including 0.5 to 0.9. In some cases, the numerical aperture of the objective is greater than the numerical aperture of an individual optical fiber that is used to probe a single region in the tissue.

The magnification of the objective may be any suitable magnification, and may be 4x or more, e.g., 10× or more, 20× or more, 40× or more, including 60× or more, and may be 100× or less, 80× or less, 60 × or less, including 20× or less. In certain embodiments, the magnification of the objective may be in the range of 4× to 100×, e.g., 10× to 60×, including 10× to 40×.

Any suitable optical fibers may be used in the present system. The optical fiber may be a multimode optical fiber. In some instances, a multimode optical fiber supports more than one propagation mode. For example, a multimode optical fiber may be configured to carry a range of wavelengths of light, where each wavelength of light propagates at a different speed.

The optical fiber may include a core defining a core diameter, where light from the light source passes through the core. The core may be further surrounded by a cladding. The core diameter of an individual optical fiber that is used to probe a single region in the tissue may vary, and may be any suitable core diameter. In some cases, the core diameter is greater than the wavelength of light carried by the optical fiber. For example, the core diameter of an optical fiber may be 10 μm or more, e.g., 50 μm or more, 100 μm or more, 200 μm or more, including 300 μm or more, and may be 1,000 μm or less, e.g., 900 μm or less, 800 μm or less, 700 μm or less, including 600 μm or less. In some embodiments, the core diameter of the individual optical fiber may be in the range of 10 to 1,000 μm, e.g., 50 to 1,000 μm, 100 to 1,000 μm, 200 to 800 μm, including 300 to 600 μm.

In some instances, the cladding surrounds at least a portion of the core of the optical fiber. For instance, the cladding may surround substantially the entire outer circumferential surface of the optical fiber. In some cases, the cladding is not present on the ends of the optical fiber, such as at the end of the optical fiber that receives and transmits light to and from the illuminating unit, and the opposite end of the optical fiber that receives and transmits light to and from the neurons in the target region of interest in the subject. The cladding may be any suitable type of cladding. In some cases, the cladding has a lower refractive index than the core of the optical fiber. Suitable materials for the cladding include, but are not limited to, plastic, resin, and the like, and combinations thereof.

In some cases, the optical fiber includes an outer coating. The outer coating may be disposed on the surface of the cladding. The coating may surround substantially the entire outer circumferential surface of the optical fiber. In some cases, the coating is not present on the ends of the optical fiber, such as at the end of the optical fiber that receives and transmits light to and from the illuminating unit, and the opposite end of the optical fiber that receives and transmits light to and from the neurons in the target region of interest in the subject. The coating may be a biologically compatible coating. A biologically compatible coating includes coatings that do not significantly react with tissues, fluids, or other substances present in the subject into which the optical fiber is inserted. In some cases, a biologically compatible coating is composed of a material that is inert (i.e., non-reactive) with respect to the surrounding environment in which the optical fiber is used.

The numerical aperture of an individual optical fiber that is used to probe a single region in the tissue may vary, and can be less than the numerical aperture of the objective. Stated another way, the numerical aperture of the objective can be greater than the numerical aperture of an individual optical fiber that is used to probe a single region in the tissue. In some cases, the numerical aperture of the individual optical fiber is 90% or less, e.g., 80% or less, 75% or less, 70% or less, 65% or less, and is 10% or more, 20% or more, 30% or more, 40% or more, 50% or more, including 60% or more, of the objective numerical aperture. In some cases, the numerical aperture of the individual optical fiber is in the range of 10% to 90%, e.g., 20% to 80%, 30% to 75%, 40% to 70%, including 50% to 65%, of the objective numerical aperture. In some cases, the numerical aperture of the individual optical fiber is 0.01 or more, e.g., 0.1 or more, 0.2 or more, 0.3 or more, including 0.4 or more, and is 1.4 or less, e.g., 1.2 or less, 1.0 or less, 0.8 or less, 0.6 or less, including 0.5 or less. In certain embodiments, the numerical aperture of the individual optical fiber is in the range of 0.01 to 1.4, e.g., 0.1 to 1.0, 0.2 to 0.8, including 0.3 to 0.6.

The number of optical fibers that form the optical fiber bundle, each of which are used to direct light stimulus from the objective and to provide illumination to an individual region of the target tissue, may vary, and may be any suitable number. In some cases, the number of optical fibers in the optical fiber bundle is one or more, e.g., 2 or more, 3 or more, 4 or more, 5 or more, 6 or more, 7 or more, including 10 or more, and is 100 or less, e.g., 80 or less, 60 or less, 40 or less, 20 or less, 15 or less, 10 or less, 8 or less, 7 or less, 6 or less, including 5 or less. In certain embodiments, the number of optical fibers is in the range of 1 to 100, e.g., 2 to 60, 3 to 40, 4 to 20, including 4 to 10.

The optical fiber end that is implanted into the target tissue may have any suitable configuration suitable for illuminating a region of the tissue with a light stimulus delivered through the optical fiber and for collecting fluorescence from the illuminated region.

In some cases, the optical fiber patchcord that directs the light stimulus from the objective ends with an attachment device at each of the branched ends, where the attachment device is configured to connect to an optical fiber that is implanted in the target tissue. Any suitable attachment device may be used. In some cases, the attachment device includes a ferrule, e.g., a metal, ceramic or plastic ferrule. The ferrule may have any suitable dimensions. In some cases, the ferrule has a diameter in the range of 0.5 to 3 mm, e.g., 0.75 to 2.5 mm, or 1 to 2 mm.

The image detector may be any suitable image detector. In some instances, the image detector is a digital camera, such as a complementary metal-oxide-semiconductor (CMOS) camera (e.g., a scientific CMOS (sCMOS) camera), or a charge-coupled device (CCD) camera (e.g., an electron-multiplying CCD (EMCCD) camera). In some cases, the image detector includes an image sensor, which is configured to detect light directed to the image detector by the optical fiber.

The present system may include any suitable electronic components to control and/or coordinate the various optical components. The optical components of the present system may be controlled by a controller, e.g., to coordinate the illumination unit illuminating the sample with light pulses of different wavelengths and/or the recording of the image with the image detector. The controllers may include a driver for the light sources that control the intensity and/or frequency of the light pulses. The controller (e.g., the driver for the light sources) may also be configured to control the wavelength of light emitted from an individual light source. The controllers may be in communication with components of the illumination unit (e.g. the light sources, collimators, shutters, filter wheels, moveable mirrors, lenses, etc.) and the image detector.

In some embodiments, the present system includes a computational unit configured to control and/or coordinate the light stimulus and image capture through one or more controllers, and to analyze images recorded by the image detector. A computational unit of the present system may include any suitable components to analyze the recorded images. Thus, the system may include one or more of the following: a processor; a non-transient, computer-readable memory, such as a computer-readable medium; an input unit, such as a keyboard, mouse, touchscreen, etc.; an output unit, such as a monitor, screen, speaker, etc.; a network interface, such as a wired or wireless network interface; and the like.

In some cases, the system may include a computer-readable medium containing instructions that can be executed by a processor, which in turn causes the system to perform any suitable portion of a method of the present disclosure, using components of the system.

Methods

A general implementation of a method of the present disclosure may include first illuminating a region or several regions of a target tissue (e.g., several distinct regions of the target tissue) with a light stimulus. The light stimulus includes light centered around a suitable wavelength and pulsed at a known interval to generate a generally intermittent pattern of illumination for a particular wavelength. The light may be pulsed at a regular interval, defined by a frequency and a pulse length. The light pattern may also be defined by a duty cycle, where the duty cycle is the percentage of a time period during which a signal, i.e., the light, is on.

The light stimulus may include a first set of light pulses at a first wavelength, and a second set of light pulses at one or more wavelengths. In some cases, the first wavelength is different from the one or more wavelengths in the second set of light pulses. The second set of light pulses may include one or more subsets of light pulses, each subset having a wavelength. In some instances, the second set of light pulses includes two or more subsets of light pulses, each subset having a different wavelength. The second set of light pulses may include a first subset of light pulses at a second wavelength, and the second set of light pulses may further include a second subset of light pulses at a third wavelength, and so on up until any suitable number of subsets of light pulses. In some cases, the wavelength of the light pulses of the first set is a different wavelength from the one or more wavelengths of light pulses of the second set. For example, the wavelength of the light pulses of the first set is a different wavelength from the second wavelength, and the wavelength of the light pulses of the first set is a different wavelength from the third wavelength.

The light pulses of the first set and the light pulses of the second set may be timed so that they do not overlap with each other. Thus, in some cases, each light pulse of the first set is interleaved among light pulses of the second set. In some cases, light pulses of the first set and light pulses of the second set alternate one after another (FIG. 1A, lower left inset, where 410 nm light pulses alternate with 470 nm light pulses). In some cases, the light pulses of the first set are timed to be at every other interval between light pulses of the second set (i.e., at half the frequency of the light pulses of the second set). Any other suitable relative timing of light pulses of the first set and second set may be used, where the light pulses of the first set and the light pulses of the second set do not overlap with each other. Light pulses of different subsets of the second set may be timed to be synchronous, simultaneous, and/or may be overlapping, or may not be overlapping.

The light stimulus is delivered to a region in a tissue of interest by a light conduit that includes one or more optical fibers, e.g., one or more multimode optical fibers, where one end of the conduit collects the light stimulus (e.g., light stimulus generated by an illumination unit and focused with an objective, as described above) and the other end is configured to illuminate the region in the tissue with the light stimulus. For example, the other end of the conduit may be configured to be implanted into the tissue at the region to illuminate the region with the light stimulus.

Each region illuminated by the light stimulus may contain excitable cells, e.g., neurons that contain one or more cellular electrical activity-dependent fluorescent moieties, e.g., neural activity-dependent fluorescent moieties, such as a genetically-encoded calcium indicator. Thus, the cells labeled with a cellular electrical activity-dependent fluorescent moiety may emit fluorescent when stimulated by a light stimulus of an appropriate wavelength and intensity, where the intensity of the fluorescence depends on the electrical activity of the cell. In some cases, an electrically active cell, e.g., a more depolarized cell, labeled with a cellular electrical activity-dependent fluorescent moiety will emit a stronger fluorescence when stimulated by a light stimulus at the excitation wavelength of the activity-dependent fluorescent moiety and having sufficient intensity compared to a cell that is not electrically active, e.g., a more hyperpolarized cell, labeled with the activity-dependent fluorescent moiety and stimulated by the same light stimulus. Depending on the wavelength of the light pulses, the region may emit fluorescence that is activity-dependent, or activity-independent.

The wavelength of light pulses of the second set may be at an excitation wavelength of a cellular electrical activity-dependent fluorescent moiety in the cells of the region illuminated by the light stimulus. Thus, a labeled cell in a region can emit a fluorescence that is representative of the activity level of the cell when the region is illuminated by at least some of the light pulses of the second set.

The fluorescence emitted by the illuminated region can be collected by the same optical fiber used to deliver the light stimulus, e.g., the same optical fiber implanted at the illuminated region. Thus, a single optical fiber illuminates cells in a single region of the tissue of interest, and collects the fluorescence emitted by the labeled cells in the region. When the region is illuminated by a light pulse having a wavelength at the excitation wavelength of the activity-dependent fluorescent moiety, the collected fluorescence may be representative of an average level of activity of the cells in the region.

The present method can include recording, at the end of the optical fiber opposite the implanted end, the fluorescence collected at the implanted end of the optical fiber. The recording may be done by an image detector (e.g., a digital camera) configured to capture an image of the cross-section of the terminal end of the optical fiber. As the optical fiber collects fluorescence representative of an average level of activity of the cells in the region at the implanted end, the fluorescence emitted at the recording end is also representative of an average level of cellular activity of the region. In some instances, the fluorescence emitted at the recording end of the optical fiber does not preserve the spatial information about the origin of fluorescence with respect to individual cells within the region illuminated by the optical fiber. Thus, the average level of fluorescence across the terminal cross-section of the optical fiber recorded by the image detector may be indicative of the aggregate activity of labeled cells in the illuminated region.

The image detector may be controlled to separately record at least one image for the duration of each light pulse. In other words, a set of one or more images may be recorded for fluorescence emitted in response to a light pulse of the first set of light pulses, and a separate set of one or more images may be recorded for fluorescence emitted in response to a light pulse (which may include one or more wavelengths of light pulses from one or more subset of light pulses) of the second set of light pulses. In some cases, a single image is recorded for each light pulse. In some cases, a single image is recorded for each light pulse of the second set of light pulses. Any other suitable timing of recording may be used. Any number of images may be recorded to obtain an image stack that shows a change in fluorescence emitted by the region of the target tissue over time.

The present method can include analyzing the recorded image, or a portion thereof, to obtain a measure of the cellular electrical activity level of the region of the target tissue. Any suitable method may be used to analyze the image. In some cases, the analyzing includes selecting a region of interest within which region the level of fluorescence is to be measured. As the images can contain the terminal cross-section of the optical fibers, the analyzing may include demarcating the terminal cross-section as the region of interest and measuring the fluorescence intensity within the terminal cross-section. The analyzing may include calculating the average intensity of fluorescence over the region of interest. The analyzing may include any other suitable data processing procedures, including, but limited to, background subtracting, normalizing, thresholding, curve fitting, subtracting bleaching artifacts, smoothing, etc., and combinations thereof.

The target tissue may be any suitable target tissue that contains one or more regions with electrically excitable cells. In some cases, the target tissue includes a plurality of regions with electrically excitable cells that are functionally interconnected, such that electrical activity in one region can modulate the electrical activity in another region. The electrically excitable cell may be any suitable electrically excitable cell, including, but not limited to a neuron or muscle cell. In some cases, the target tissue is neural tissue, e.g., brain, spinal cord, etc. In some cases, the target tissue is the heart, gastrointestinal tract, lung, skeletal muscle, etc.

In some cases, the method further includes illuminating a region in a target tissue with a first set of light pulses at the isosbestic point of a cellular electrical activity-dependent fluorescent moiety used to label the excitable cells in the region. The fluorescence signal emitted in response to the first set of light pulses may then be independent of the level of electrical activity of the excitable cell. Thus, the recorded trace of the fluorescence signal obtained at the isosbestic point of the cellular electrical activity-dependent fluorescent moiety may serve as a control to correct for, e.g., subtract out, the non-cellular electrical activity-related component in the measured cellular electrical activity-dependent fluorescence level.

In certain embodiments, the present method further includes illuminating a region in a target tissue, where the region includes neurons that contain either one or both of two cellular electrical activity-dependent fluorescent moieties and the two activity-dependent fluorescent moieties have different (and distinguishable) excitation and emission wavelengths. Thus, the second set of light pulses used to illuminate the region may include two subsets of light pulses at different wavelengths, each of which is at the excitation wavelength of one or the other activity-dependent fluorescent moiety. Light pulses of the two subsets may be simultaneous, synchronous, or non-overlapping. The fluorescence emitted from the illuminated region may include fluorescence at two wavelengths, each of which may be representative of cellular electrical activity in the cell that is labeled with the activity-dependent fluorescent moiety that produced the respective fluorescence. Thus, in some cases, a first collection of cells may be labeled with a first activity-dependent fluorescent moiety, which emits fluorescence at a first wavelength that is representative of cellular electrical activity in the first collection of cells, and a second collection of cells may be labeled with a second activity-dependent fluorescent moiety, which emits fluorescence at a second wavelength that is representative of cellular electrical activity in the second collection of cells. The activity-dependent fluorescence at the two different wavelengths can be collected simultaneously with the optical fiber (e.g., multimode optical fiber) that illuminated the region, and the combined fluorescence can be directed to the image detector and recorded. In some cases, the fluorescence emitted from the region is split, e.g., using an image splitter, to from separate images for the fluorescence emitted by the cells expressing the first activity-dependent fluorescent moiety and for the fluorescence emitted by the cells expressing the second activity-dependent fluorescent moiety. Thus, the method may include recording a first image of the terminal cross-section of the optical fiber for a region, where the a cross-sectional average of the fluorescence is representative of an aggregate neural activity of a first collection of neurons labeled with the first neural activity-dependent fluorescent moiety, and a second image of the terminal cross-section of the optical fiber for a region, where the a cross-sectional average of the fluorescence is representative of an aggregate neural activity of a second collection of neurons labeled with the second neural activity-dependent fluorescent moiety. As such, the aggregate neural activities of the first collection of neurons and the second collection of neurons measured by the present method are contemporaneous aggregate neural activities. Where a region in a target tissue contains neurons that are labeled with multiple neural activity-dependent fluorescent moieties, all or at least some of the fluorescent moieties may share the same isosbestic point.

In some cases, the method includes illuminating a plurality of regions of a target tissue using a plurality of optical fibers, where each region contains a plurality of excitable cells, e.g., neurons, labeled with a cellular electrical activity-dependent fluorescent moiety, and where one optical fiber illuminates and collects fluorescence from one region. The recording may include simultaneously recording onto a frame of the image detector the terminal cross-sections of each of the optical fibers, where each optical fiber terminal cross-section conveys fluorescence that is representative of a corresponding region in the tissue at which the optical fiber is implanted. For example, the recording may include simultaneously detecting using the image sensor of the image detector light from the terminal cross-sections of each of the optical fibers. As described herein, the light detected by the image sensor may include fluorescence generated in response to the light pulses used to excite the neural activity-dependent fluorescent moieties in the region of interest.

The number of optical fibers used in the present method may vary, and may be any suitable number. In some cases, the number of optical fibers used to excite and image different regions of the target tissue is one or more, e.g., 2 or more, 3 or more, 4 or more, 5 or more, 6 or more, 7 or more, including 10 or more, and is 100 or less, e.g., 80 or less, 60 or less, 40 or less, 20 or less, 15 or less, 10 or less, 8 or less, 7 or less, 6 or less, including 5 or less. In certain embodiments, the number of optical fibers is in the range of 1 to 100, e.g., 2 to 60, 3 to 40, 4 to 20, including 4 to 10.

Any suitable optical fibers may be used in the present method. The optical fiber may be a multimode optical fiber. The optical fiber may include a core defining a core diameter, where light passes through the core. The core may be further surrounded by a cladding. The core diameter of an individual optical fiber that is used to probe a single region in the tissue may vary, and may be 10 μm or more, e.g., 50 μm or more, 100 μm or more, 200 μm or more, including 300 μm or more, and may be 1,000 μm or less, e.g., 900 μm or less, 800 μm or less, 700 μm or less, including 600 μm or less. In some embodiments, the core diameter of the individual optical fiber may be in the range of 10 to 1,000 μm, e.g., 50 to 1,000 μm, 100 to 1,000 μm, 200 to 800 μm, including 300 to 600 μm.

The numerical aperture of an individual optical fiber that is used to probe a single region in the tissue may vary, and can be less than the numerical aperture of the objective. In some cases, the numerical aperture of the individual optical fiber is 90% or less, e.g., 80% or less, 75% or less, 70% or less, 65% or less, and is 10% or more, 20% or more, 30% or more, 40% or more, 50% or more, including 60% or more, of the objective numerical aperture. In some cases, the numerical aperture of the individual optical fiber is in the range of 10% to 90%, e.g., 20% to 80%, 30% to 75%, 40% to 70%, including 50% to 65%, of the objective numerical aperture. In some cases, the numerical aperture of the individual optical fiber is 0.01 or more, e.g., 0.1 or more, 0.2 or more, 0.3 or more, including 0.4 or more, and is 1.4 or less, e.g., 1.2 or less, 1.0 or less, 0.8 or less, 0.6 or less, including 0.5 or less. In certain embodiments, the numerical aperture of the individual optical fiber is in the range of 0.01 to 1.4, e.g., 0.1 to 1.0, 0.2 to 0.8, including 0.3 to 0.6.

The present method may use any suitable image detector. In some instances, the image detector is a digital camera, such as a CMOS camera (e.g., a sCMOS camera), or a charge-coupled device (CCD) camera (e.g., an electron-multiplying CCD (EMCCD) camera).

The collection of neurons whose activity is to be measured by the present method may be any suitable collection of neurons. In some cases, a collection of neurons is defined by a known functional classification. Any convenient functional classification may be used to define the collection of neuron. In some cases, the collection of neurons includes excitatory neurons, inhibitory neurons, sensory neurons, motor neurons, interneurons, etc. In some cases, the collection of neurons includes dopaminergic, cholinergic, GABAergic, glutamatergic, or peptidergic neurons. In some cases, the collection of neurons includes Purkinje cells, pyramidal cells, golgi cells, Lugaro cells, basket cells, candelabrum cells, granule cells, stellate cells, unipolar brush cells, medium spiny neurons, Renshaw cells, spindle cells, etc. The different functional cells may be labeled specifically with a cellular electrical activity-dependent fluorescent moiety using any suitable method. In some cases, a cell-specific promoter, or a combination of different cell-specific promoters, may be used to control expression of a genetically-encoded cellular electrical activity-dependent fluorescent moiety, e.g., a genetically-encoded calcium indicator, specifically in a functionally-defined collection of neurons.

The target tissue can be a human target tissue (e.g., an in vivo, in vitro, or ex vivo target tissue). The target tissue can be a non-human animal target tissue (e.g., an in vivo, in vitro, or ex vivo target tissue). Non-human animals include non-human primates, murines (e.g., rats, mice), lagomorphs (e.g., rabbits), ungulates, felines, canines, and the like. The target tissue can be in a live human or non-human animal. The target tissue can be in a freely-moving human or non-human animal.

The present method may include illuminating any suitable region of the target tissue, e.g., the brain. In some cases, the method includes illuminating a functionally and/or anatomically defined region of a brain, e.g., a amphibian brain, a reptile brain, a bird brain, a marsupial brain, mammalian brain, etc. In some cases, the method includes illuminating at least of portion of the ventral tegmental area (VTA), prefontal cortex (PFC), nucleus accumbens (NAc), amygdala (BLA), substantia nigra, ventral pallidum, globus pallidus, dorsal striatum, ventral striatum, subthalamic nucleus, hippocampus, dentate gyrus, cingulate gyrus, entorhinal cortex, olfactory cortex, sensory cortex, thalamus, primary motor cortex, and cerebellum, etc., of a mammalian brain. Any other suitable functionally and/or anatomically defined region of a mammalian brain may be illuminated in the present method.

In some cases, the method includes illuminating a region of the brain where the cell body of labeled neurons is present. In some cases, the method includes illuminating a region of the brain where the neuronal projections, e.g., axonal projections, dendritic projections, etc., of labeled neurons are present.

In some cases, where two or more regions are illuminated and whose cellular electrical activities are recorded, the method includes illuminating regions that are functionally distinct. Two regions may be functionally distinct by being two distinct anatomical regions. Two regions may be functionally distinct by containing different functional types of population of neurons. Two regions may be functionally distinct by having distinct types of inputs or outputs to other regions of the brain, and/or different functional types of neurons. Two regions may be functionally distinct by any other suitable criteria.

In some cases, two or more regions that are illuminated and whose cellular electrical activity is recorded by the present method may be functionally connected regions of the target tissue, e.g., the brain. A functionally connected regions of the brain may have neurons from one region that are connected on average to neurons of a second region by a minimum number of synaptic connections of one or more, e.g., two or more, 3 or more, 4 or more, including 5 or more, and by a minimum number of synaptic connections of 10 or less, 9 or less, 8 or less, 7 or less, 6 or less 5 or less, 4 or less, including 3 or less.

In some embodiments, the target tissue whose region(s) are illuminated and whose cellular electrical activity is recorded by the present method is an in vivo tissue, or an ex vivo tissue (e.g., a tissue slice). In some cases, the target tissue is in a freely moving animal, or is in a head-fixed animal. In some cases, the target tissue is in an animal that has been exposed to an environmental manipulation. In some cases, the target tissue is in an animal that has been conditioned to respond, behaviorally and/or neurologically, more reliably to a stimulus compared to an animal that has not been conditioned. In some cases, the animal is a water-deprived animal; a water-deprived animal rewarded with water; a food-deprived animal; a food-deprived animal rewarded with food; a solitary animal; an animal in the presence of another animal of the same species; an animal presented with an aversive stimulus, e.g., an electric shock, aversive sounds, such as a loud noise, extreme temperatures, repulsive odors, etc.; an animal presented with a novel object; an animal navigating a maze; an animal performing a memory/recollection task; etc.

The present method may employ any suitable frequency of light pulses. In some cases, the frequency of the light pulses is 0.1 Hz or more, e.g., 1 Hz or more, 5 Hz or more, 10 Hz or more, 15 Hz or more, 20 Hz or more, including 25 Hz or more, and is 1,000 Hz or less, e.g., 500 Hz or less, 200 Hz or less, 100 Hz or less, 80 Hz or less, including 60 Hz or less. In certain embodiments, the frequency of the light pulses is in the range of 0.1 to 1,000 Hz, e.g., 1 to 500 Hz, 1 to 200 Hz, 5 to 80 Hz, 10 to 60 Hz, including 15 to 60 Hz.

The present method may employ any suitable duration of a pulse of light to illuminate a region in a target tissue. In some cases, the duration of a light pulse is 1.0 ms or more, e.g., 2.0 ms or more, 5.0 ms or more, 10.0 ms or more, 15 ms or more, 20 ms or more, including 25 ms or more, and is 1,000 ms or less, e.g., 500 ms or more, 300 ms or less, 200 ms or less, 100 ms or less, 50 ms or less, including 40 ms or less. In some embodiments, the duration of a light pulse is in the range of 1.0 to 1,000 ms, e.g., 2.0 to 500 ms, 5.0 to 200 ms, 10.0 to 100 ms, including 15 to 50 ms.

The present method may employ any suitable duty cycle for the pulse of light used to illuminate a region in a target tissue. In some cases, the duty cycle of the light pulse is 5% or more, such as 10% or more, or 15% or more or 20% or more, or 25% or more, or 30% or more, or 35% or more, or 40% or more, or 45% or more, or 50% or more, or 55% or more, or 60% or more, or 65% or more, or 70% or more, or 75% or more, including 100% or less, such as 95% or less, or 90% or less, or 85% or less, or 80% or less, or 75% or less, or 70% or less, or 65% or less, or 60% or less, or 55% or less, or 50% or less. In some embodiments, the duty cycle of the light pulse is in the range of 5% to 75%, such as 10% to 70%, or 10% to 65%, or 10% to 60%, or 10% to 55%, or 10% to 50%, or 15% to 45%, or 15% to 40%, or 15% to 35%, or 20% to 30%. In certain instances, the duty cycle of the light pulse is 25%.

The power of the light pulses used to illuminate a region of a target tissue may be any suitable power. The power of the light pulse may be the power measured at the end of the patchcord, i.e., at the end of the optical fiber at the surface of the target tissue. In some cases, a light pulse for exciting a cellular electrical activity-dependent fluorescent moiety has a power of 0.5 μW or more, e.g., 1.0 μW or more, 2.0 μW or more, 3.0 μW or more, 5 μW or more, 10 μW or more, 15 μW or more, including 20 μW or more, and has a power of 500 μW or less, e.g., 250 μW or less, 200 μW or less, 150 μW or less, 100 μW or less, 50 μW or less, including 30 μW or less. In some cases, a light pulse for exciting a cellular electrical activity-dependent fluorescent moiety has a power in the range of 0.5 to 500 μW, e.g., 1.0 to 250 μW, 1.0 to 200 μW, 2.0 to 100 μW, 3.0 to 50 μW, including 3.0 to 30 μW. In some cases, a light pulse for exciting a cellular electrical activity-dependent fluorescent moiety has a power of 0.5 mW or more, e.g., 1.0 mW or more, 2.0 mW or more, including 5.0 mW or more, and has a power of 10 mW or less, e.g., 8.0 mW or less, 6.0 mW or less, 4.0 mW or less, including 3.0 mW or less. In some cases, a light pulse for exciting a cellular electrical activity-dependent fluorescent moiety has a power in the range of 0.5 to 10 mW, e.g., 1.0 to 8.0 mW, including 1.0 to 6.0 mW.

In some embodiments, a region illuminated by the light stimulus may contain excitable cells, e.g., neurons, that contain one or more light-activated polypeptides, e.g., light-activated ion channels or ion pumps, which, when activated by a light pulse at the activation wavelength, can modulate the electrical activity of the cells. The light-activated polypeptide may be any suitable light-activated polypeptide for modulating the activity of an excitable cell in a light-dependent manner, as described further below. The light-activated polypeptide may be a genetically encoded light-activated polypeptide expressed in the cell.

The region that is illuminated by an optical fiber, according to embodiments of the present method, may contain cells that contain both a cellular electrical activity-dependent fluorescent moiety and a light-activated polypeptide, or may contain cells that have either one of the two. Thus, the region may contain a first collection of cells that are labeled with the cellular electrical activity-dependent fluorescent moiety, and a second collection of cells that contain the light-activated polypeptide. The first collection of cells and the second collection of cells may be substantially the same collection of cells (i.e., the cells in the region contain both the cellular electrical activity-dependent fluorescent moiety and the light-activated polypeptide, if any). Alternatively, the first collection of cells and the second collection of cells may be distinct but overlapping collections of cells (i.e., some cells in the region contain both the cellular electrical activity-dependent fluorescent moiety and the light-activated polypeptide, while other cells in the region contain either the cellular electrical activity-dependent fluorescent moiety or the light-activated polypeptide, if any). In some cases, the first collection of cells and the second collection of cells may be substantially non-overlapping collections of cells (i.e., the cells in the region contain either the cellular electrical activity-dependent fluorescent moiety or the light-activated polypeptide, if any). The cells expressing the light-activated polypeptide may be a functionally-defined population of cells, as described elsewhere.

Where the region contains a collection of cells containing a light-activated polypeptide, the wavelength of the first set of light pulses may be at the activation wavelength of the light-activated polypeptide. The power of the light pulses at the activation wavelength of the light-activated polypeptide may be any suitable power for activating the light-activated polypeptide and modulating cellular electrical activity in the region. In some cases, the power of the light pulses at the activation wavelength of the light-activated polypeptide is 0.01 mW or more, e.g., 0.05 mW or more, 0.1 mW or more, 0.5 mW or more, 1.0 mW or more, 5.0 mW or more, including 10.0 mW or more, and is 50 mW or less, e.g., 40 mW or less, 30 mW or less, 20 mW or less, 10 mW or less, 5.0 mW or less, 4.0 mW or less, 3.0 mW or less, 2.0 mW or less, including 1 mW or less. In some cases, the power of the light pulses at the activation wavelength of the light-activated polypeptide is in the range of 0.01 to 50 mW, e.g., 0.05 to 5.0 mW, 0.1 mW to 4.0 mW, including 0.1 mW to 3 mW.

In some cases, the power of the light pulses at the activation wavelength of the light-activated polypeptide is sufficient to generate electrical activity in the cell that approximates electrical activity that is generated by a natural stimulus, i.e., a stimulus that is provided to the animal in which the target tissue resides as a whole, rather than specifically only to those cells that contain the light-activated polypeptide in the form of a light pulse. A natural stimulus may be a sensory stimulus provided to a sensory organ of the animal, such as, but not limited to, light to the visual system, tactile stimulus to the somatosensory system, sound to the auditory system, tastant to the gustatory system, odor to the olfactory system, etc. In some cases the natural stimulus is a reward stimulus, e.g., a water reward and/or food reward. In some cases, the natural stimulus is an aversive stimulus, e.g., an electric shock, aversive sounds, such as a loud noise, extreme temperatures, repulsive odors, etc. In some cases, the natural stimulus is a novel object. In some cases, the natural stimulus is a social cue. In some cases, the natural stimulus is a task, such as navigating a maze or performing a memory/recollection task, etc.

The activation of the light-activated polypeptide using the appropriate wavelength and power of light pulse may induce electrical activity in the cell that has a similar maximum magnitude of response as the electrical activity induced by a natural stimulus, as measured by the level of fluorescence from a neural activity-dependent fluorescent moiety expressed in the same cell. The cellular electrical activity induced by activation of the light-activated polypeptide may have a maximum magnitude that is 50% or more, e.g., 60% or more, 70% or more, 80% or more, 90% or more, 95% or more, including 100% or more, and is 200% or less, e.g., 150% or less, 120% or less, 110% or less, including 100% or less than the maximum magnitude of the cellular electrical activity induced by a natural stimulus. In some cases, the cellular electrical activity induced by activation of the light-activated polypeptide may have a maximum magnitude in the range of 50 to 200%, e.g., 60 to 150%, 70 to 120%, including 80 to 110% of the maximum magnitude of the cellular electrical activity induced by a natural stimulus. In some cases, the cellular electrical activity induced by activation of the light-activated polypeptide may have a duration of response above background that is 50% or more, e.g., 60% or more, 70% or more, 80% or more, 90% or more, 95% or more, including 100% or more, and is 200% or less, e.g., 150% or less, 120% or less, 110% or less, including 100% or less than the duration of response above background of the cellular electrical activity induced by a natural stimulus. In some cases, the cellular electrical activity induced by activation of the light-activated polypeptide may have a duration of response above background in the range of 50 to 200%, e.g., 60 to 150%, 70 to 120%, including 80 to 110% of the duration of response above background of the cellular electrical activity induced by a natural stimulus. In some cases, the cellular electrical activity induced by activation of the light-activated polypeptide may have a response latency that is 50% or more, e.g., 60% or more, 70% or more, 80% or more, 90% or more, 95% or more, including 100% or more, and is 200% or less, e.g., 150% or less, 120% or less, 110% or less, including 100% or less than the response latency of the cellular electrical activity induced by a natural stimulus. In some cases, the cellular electrical activity induced by activation of the light-activated polypeptide may have a response latency in the range of 50 to 200%, e.g., 60 to 150%, 70 to 120%, including 80 to 110% of the response latency of the cellular electrical activity induced by a natural stimulus.

In some cases, where the region contains a first collection of cells containing a light-activated polypeptide and a second collection of cells labeled with an electrical activity-dependent fluorescent moiety, the light pulse having a wavelength at the excitation wavelength of the electrical activity-dependent fluorescent moiety has a power that is sufficiently low that the light pulse does not cause activation of the light-activated polypeptide to significantly modulate electrical activity of the cell, as measured by the fluorescence from the electrical activity-dependent fluorescent moiety. In some cases, the light pulse having a wavelength at the excitation wavelength of the electrical activity-dependent fluorescent moiety has a power of 50 μW or less, e.g., 30 μW or less, 15 μW or less, 10 μW or less, including 8.0 μW or less, and has a power of 0.5 μW or more, e.g., 1.0 μW or more, 2.0 μW or more, including 3.0 μW or more. In some cases, the light pulse having a wavelength at the excitation wavelength of the electrical activity-dependent fluorescent moiety has a power in the range of 0.5 to 50 μW, e.g., 1.0 to 30 μW, 1.0 to 15 μW, 1.0 to 10 μW, including 1.0 to 8μW.

The region may contain any suitable number of distinct collections of cells, where each collection of cells is labeled with a different electrical activity-dependent fluorescent moiety. In some cases, the region contains 1 or more, e.g., 2 or more, 3 or more, including 4 or more, distinct collections of cells, and contains 10 or fewer, e.g., 9 or fewer, 8 or fewer, 7 or less, 6 or fewer, including 5 or fewer distinct collections of cells. In some cases, the region contains in the range of 1 to 10, e.g., 1 to 8, 2 to 6, 2 to 5, including 2 to 4 collections of cells. In some cases, the method includes illuminating the region with a light stimulus containing light pulses at an excitation wavelength for some or all of the different electrical activity-dependent fluorescent moieties in the region. For example, a multimode optical fiber as described herein may be used to illuminate the region with a light stimulus containing two or more light pulses at different excitation wavelengths for different electrical activity-dependent fluorescent moieties in the region.

The present method can be a rapid method of measuring cellular electrical activity, e.g., neural activity, in one or more regions of a target tissue, e.g., a brain. In some cases, the present method provides real-time measurement of cellular electrical activity, in one or more regions of a target tissue. In some cases, the method can be performed in 20 ms or less, e.g., 10 ms or less, 8 ms or less, 6 ms or less, 5 ms or less, 4 ms or less, including 3 ms or less, and can be performed in 1 ms or more, 2 ms or more, 3 ms or more, including 4 ms or more. In some cases, the method can be performed in a range of 1 to 20 ms, e.g., 1 to 10 ms, 2 to 8 ms, including 2 to 6 ms. In some cases, the aggregate neural activity of 2 or more, e.g., 3 or more, 5 or more, 7 or more, including 10 or more, and 50 or less, e.g., 30 or less, 20 or less, including 15 or less regions of a target tissue can be analyzed synchronously using the present method in 20 ms or less, e.g., 10 ms or less, 8 ms or less, 6 ms or less, 5 ms or less, 4 ms or less, including 3 ms or less, and can be performed in 1 ms or more, 2 ms or more, 3 ms or more, including 4 ms or more. In some cases, the aggregate neural activity of 2 or more, e.g., 3 or more, 5 or more, 7 or more, including 10 or more, and 50 or less, e.g., 30 or less, 20 or less, including 15 or less regions of a target tissue can be analyzed synchronously using the present method in 1 to 20 ms, e.g., 1 to 10 ms, 2 to 8 ms, including 2 to 6 ms.

In some embodiments, the method is a method for closed-loop control of cellular electrical activity in a target tissue. In some cases, where a first region of the target tissue contains a collection of cells containing a light-activated polypeptide, the method further includes illuminating the first region with the cells containing a light-activated polypeptide with a light pulse at the activation wavelength of the light-activated polypeptide, where the timing and/or power of the illuminating the first region with the cells containing a light-activated polypeptide is based on an recorded image of a terminal cross-section of an optical fiber from a second region and the analysis of the aggregate neural activity in the second region. Thus, in some cases, the analysis of the aggregate neural activity in the second region may indicate that first region should be illuminated by a light pulse to activate a depolarizing light-activated polypeptide at a certain intensity and for a specific duration, e.g., to compensate for a lack of activity in the second region. In some cases, the analysis of the aggregate neural activity in the second region may indicate that first region should be illuminated by a light pulse to activate a hyperpolarizing light-activated polypeptide at a certain intensity and for a specific duration, e.g., to reduce hyperactivity in the second region.

Cellular Electrical Activity-Dependent Fluorescent Moieties

The cellular electrical activity-dependent fluorescent moieties, e.g., the neural activity-dependent fluorescent moieties, may include any suitable fluorescent moiety whose fluorescence properties are responsive to the electrical activity of the cell in which it resides. Fluorescent moieties whose fluorescence properties are sensitive to cellular electrical activity include ratiometric/non-ratiometric dyes and fluorescent proteins. Fluorescent moieties whose fluorescence properties are sensitive to cellular electrical activity may be a fluorescence resonance energy transfer (FRET)-based reporter. Fluorescent moieties whose fluorescence properties are sensitive to cellular electrical activity may be sensitive to changes in intracellular concentration of ions such as calcium, sodium and protons or to changes in membrane potential. In such cases, fluorescent dyes of interest include, but are not limited to, calcium indicator dyes (Indo-1, Fura-2, and Fluo-3, Calcium Green®, Fluo-4, etc.); sodium indicator dyes (sodium-binding benzofuran isophthalate (SBFI), Sodium Green™, CoroNa™ Green, CoroNa™ Red, etc.); and proton indicator dyes (2′,7′-bis-(carboxyethyl)-5-(and-6)-carboxyfluorescein (BCECF), etc.).

Cellular electrical activity-dependent fluorescent proteins of interest include, but are not limited to, genetically encoded calcium indicators (Cameleon, Pericam, TN-XXL, Twitch, GECO, GCaMP1, GCaMP2, GCaMP3, GCaMP6 and derivatives thereof, as well as those cited in U.S. Pat. No. 8,629,256, and Tian et al. 2012 Prog Brain Res, 196:79, which are incorporated herein by reference); and genetically encoded voltage indicators (QuasAr1, QuasAr2, VSFP, and derivatives thereof, as well as those cited in US App. Pub. No. 2013/0224756, Hochbaum et al., Nat Methods 2014 11:825, Baker et al. Brain Cell Biol 2008 36:53; and Mutoh et al., Exp Physiol 2011 96:13, each of which are incorporated herein by reference). Other suitable GCaMP-based genetically encoded calcium indicators include GCaMP2.1, GCaMP2.2a, GCaMP2.2b, GCaMP2.3, GCaMP2.4, GCaMP3, GCaMP5g, GCaMP6m, GCaMP6s, GCaMP6f, etc. Suitable GECO-based genetically encoded calcium indicators include G-GECO1, G-GECO1.1 and G-GECO1.2, the red fluorescing indicator R-GECO1, the blue fluorescing indicator B-GECO1, the emission ratiometic indicator GEM-GECO1, and the excitation ratiometric GEX-GECO1, etc.

A suitable genetically encoded calcium indicator polypeptide can comprise an amino acid sequence having at least 75%, at least 80%, at least 85%, at least 90%, at least 95%, at least 98%, at least 99%, or 100%, amino acid sequence identity with an amino acid sequence set forth in FIG. 13A-13S. A suitable genetically encoded calcium indicator polypeptide can comprise an amino acid sequence having at least 75%, at least 80%, at least 85%, at least 90%, at least 95%, at least 98%, at least 99%, or 100%, amino acid sequence identity with an amino acid sequence set forth in FIGS. 14A-14C.

In some cases, the fluorescent moiety may be sensitive to biochemical changes in the excitable cell, such as changes in enzymatic activity (e.g., activation of kinases); changes in binding interactions (e.g., binding of transcription factors to DNA); changes in subcellular localization of proteins; etc. Exemplary fluorescent moieties are further described in, e.g, Mehta et al., Annu Rev Biochem. 2011; 80: 375, which is incorporated herein by reference.

Light-Activated Polypeptides

Where region of the target tissue includes cells that contain a light-activated polypeptide, the light-activated polypeptide may be any suitable light-activated polypeptide for modulating the electrical activity of the cell with a light stimulus. In some instances, the light-activated polypeptide is a light-activated ion channel polypeptide. The light-activated ion channel polypeptides are adapted to allow one or more ions to pass through the plasma membrane of a target cell when the polypeptide is illuminated with light of an activating wavelength. Light-activated proteins may be characterized as ion pump proteins, which facilitate the passage of a small number of ions through the plasma membrane per photon of light, or as ion channel proteins, which allow a stream of ions to freely flow through the plasma membrane when the channel is open. In some embodiments, the light-activated polypeptide depolarizes the cell when activated by light of an activating wavelength. In some embodiments, the light-activated polypeptide hyperpolarizes the cell when activated by light of an activating wavelength. Suitable hyperpolarizing and depolarizing polypeptides are known in the art and include, e.g., a channelrhodopsin (e.g., ChR2), variants of ChR2 (e.g., C128S, D156A, C128S+D156A, E123A, E123T), iC1C2, C1C2, GtACR2, NpHR, eNpHR3.0, C1V1, VChR1, VChR2, SwiChR, Arch, ArchT, KR2, ReaChR, ChiEF, Chronos, ChRGR, CsChrimson, and the like. In some cases, the light-activated polypeptide includes bReaCh-ES, as described herein and described further in, e.g., Rajasethupathy et al., Nature. 2015 Oct. 29; 526(7575):653, which is incorporated by reference. Hyperpolarizing and depolarizing opsins have been described in various publications; see, e.g., Berndt and Deisseroth (2015) Science 349:590; Berndt et al. (2014) Science 344:420; and Guru et al. (Jul. 25, 2015) Intl. J. Neuropsychopharmacol. 18:pyv079 (PMID 26209858).

As non-limiting examples, a suitable light-activated polypeptide can comprise an amino acid sequence having at least 75%, at least 80%, at least 85%, at least 90%, at least 95%, at least 98%, at least 99%, or 100%, amino acid sequence identity with an amino acid sequence set forth in any one of FIG. 15A-15U. A bReaChES light-activated polypeptide can comprise an amino acid sequence having at least 75%, at least 80%, at least 85%, at least 90%, at least 95%, at least 98%, at least 99%, or 100%, amino acid sequence identity with an amino acid sequence set forth in any one of FIG. 12B-12F.

Cells in a region of the target tissue may be labeled with a cellular activity-dependent fluorescent moiety and/or the light-activated polypeptide may be introduced into the cells using any suitable method. In some cases, the cells in the region are genetically modified to express a genetically-encoded fluorescent moiety, e.g., a genetically-encoded calcium or voltage indicator, and/or a light-activated polypeptide. In some cases, the cells may be genetically modified using a viral vector, e.g., an adeno-associated viral vector, containing a nucleic acid having a nucleotide sequence that encodes the cellular activity-dependent fluorescent moiety and/or a light-activated polypeptide. The viral vector may include any suitable control elements (e.g., promoters, enhancers, recombination sites, etc.) to control expression of the cellular activity-dependent fluorescent moiety and/or a light-activated polypeptide according to cell type, timing, presence of an inducer, etc.

Neuron-specific promoters and other control elements (e.g., enhancers) are known in the art. Suitable neuron-specific control sequences include, but are not limited to, a neuron-specific enolase (NSE) promoter (see, e.g., EMBL HSENO2, X51956; see also, e.g., U.S. Pat. Nos. 6,649,811, 5,387,742); an aromatic amino acid decarboxylase (AADC) promoter; a neurofilament promoter (see, e.g., GenBank HUMNFL, L04147); a synapsin promoter (see, e.g., GenBank HUMSYNIB, M55301); a thy-1 promoter (see, e.g., Chen et al. (1987) Cell 51:7-19; and Llewellyn et al. (2010) Nat. Med. 16:1161); a serotonin receptor promoter (see, e.g., GenBank S62283); a tyrosine hydroxylase promoter (TH) (see, e.g., Nucl. Acids. Res. 15:2363-2384 (1987) and Neuron 6:583-594 (1991)); a GnRH promoter (see, e.g., Radovick et al., Proc. Natl. Acad. Sci. USA 88:3402-3406 (1991)); an L7 promoter (see, e.g., Oberdick et al., Science 248:223-226 (1990)); a DNMT promoter (see, e.g., Bartge et al., Proc. Natl. Acad. Sci. USA 85:3648-3652 (1988)); an enkephalin promoter (see, e.g., Comb et al., EMBO J. 17:3793-3805 (1988)); a myelin basic protein (MBP) promoter; a CMV enhancer/platelet-derived growth factor-β promoter (see, e.g., Liu et al. (2004) Gene Therapy 11:52-60); a motor neuron-specific gene Hb9 promoter (see, e.g., U.S. Pat. No. 7,632,679; and Lee et al. (2004) Development 131:3295-3306); and an alpha subunit of Ca(²⁺)-calmodulin-dependent protein kinase II (CaMKIIα) promoter (see, e.g., Mayford et al. (1996) Proc. Natl. Acad. Sci. USA 93:13250). Other suitable promoters include elongation factor (EF) 1α and dopamine transporter (DAT) promoters.

In some cases, cell type-specific expression of the cellular activity-dependent fluorescent moiety and/or a light-activated polypeptide may be achieved by using recombination systems, e.g., Cre-Lox recombination, Flp-FRT recombination, etc. Cell type-specific expression of genes using recombination has been described in, e.g., Fenno et al., Nat Methods. 2014 July; 11(7):763; and Gompf et al., Front Behav Neurosci. 2015 Jul. 2; 9:152, each of which are incorporated by reference herein.

EXAMPLES

The following examples are put forth so as to provide those of ordinary skill in the art with a complete disclosure and description of how to make and use the disclosed subject matter, and are not intended to limit the scope of what the inventors regard as their invention nor are they intended to represent that the experiments below are all or the only experiments performed. Efforts have been made to ensure accuracy with respect to numbers used (e.g. amounts, temperature, etc.) but some experimental errors and deviations should be accounted for. Unless indicated otherwise, parts are parts by weight, molecular weight is weight average molecular weight, temperature is in degrees Celsius, and pressure is at or near atmospheric. Ø denotes the core diameter. Standard abbreviations may be used, e.g., bp, base pair(s); kb, kilobase(s); pl, picoliter(s); s or sec, second(s); min, minute(s); h or hr, hour(s); aa, amino acid(s); kb, kilobase(s); bp, base pair(s); nt, nucleotide(s); i.m., intramuscular(ly); i.p., intraperitoneal(ly); s.c., subcutaneous(ly); and the like.

Example 1 Materials and Methods

The following materials and methods were used in the Examples.

Core Frame-Projected Independent-Fiber Photometry (FIP) Platform Setup and Modifications

The main FIP platform included a widefield microscope imaging a bundle of one or more (up to 7 in this example) fiber faces, with a series of dichroic mirrors integrated in the microscope to be able to simultaneously couple in various wavelength excitation light sources. Custom MATLAB® (Mathworks) software was used to control the timing of the various excitation light sources, to synchronously acquire camera frames, and to digitally sum and compute the total fluorescence from each of the fibers in each camera frame in real-time. The excitation light sources, dichroics, and acquisition timing protocols were reconfigurable to support combinations of dual-color recording, simultaneous recording and stimulation, and concurrent acquisition of isosbestic control signals.

A custom patchcord of 7 bundled 400 μm Ø 0.48 numerical aperture (NA) fibers (Doric Lenses) was used for FIP experiments. One end of the patchcord terminated in a SubMiniature version A (SMA) connector mounted (Thorlabs, SM1SMA) at the working distance of the objective, while the other end terminated in 7 individual 1.25 mm Ø stainless steel ferrules. These ferrules were coupled via ceramic sleeves (Thorlabs, ADAL1) to 1.25 mm Ø ferrules implanted into a mouse.

The fiber faces were imaged through a 20×/0.75 NA objective (Nikon, CFI Plan Apo Lambda 20×) through a series of reconfigurable dichroic mirrors. Fluorescence emission from the fibers passed through a 535 nm bandpass fluorescence emission filter (selected for GCaMP recording; Semrock FF01-535/22-25). The fluorescence image was focused onto the sensor of a scientific complementary metal-oxide semiconductor (sCMOS) camera (Hamamatsu ORCA®-Flash4.0) through a tube lens (Thorlabs AC254-035-A-ML). The reconfigurable dichroic mirrors were mounted in removable dichroic cube holders (Thorlabs, DFM1), and enabled two total light sources to be coupled in. In the standard configuration, a 470 nm light emitting diode (LED) (Thorlabs, M470F1), was fiber coupled into the dichroic cube holder by using a 1000 μm Ø, 0.48 NA fiber (Thorlabs, M71L01) and a 405 nm, f=4.02 mm, 0.6 NA collimator (Thorlabs, F671SMA-405 and AD11F) with a 495 nm longpass dichroic mirror (Semrock, FF495-Di02-25×36). This produced an excitation spot of ˜2.5 mm Ø (10 mm÷4.02 mm×1000 μm) at the working distance of the 20× objective (focal length of ˜10 mm). This spot was sufficiently large to fill all of the fibers of the 7-fiber branching patchcord. Typically the light powers emitted from the different fibers were within 25-50% of each other. All of the LEDs used were controlled by a driver enabling digital modulation up to 1 kHz (Thorlabs, LEDD1B). See Example 2 for additional system design, alignment, and calibration considerations.

Time-division multiplexing. To enable the concurrent recording of multiple channels per fiber (or for simultaneous optogenetic stimulation), a time-division multiplexing strategy was used to time-sequentially sample each channel individually. Schematics of the time-division multiplexing strategy used for each experiment are shown in FIG. 1A, FIG. 8B, and FIG. 2F. Briefly, for GCaMP6 imaging, consecutive camera frames were captured using alternating 470 nm and 410 nm excitation sources; i.e., every other camera frame was captured using either 470 nm or 410 nm light. For example if the camera is capturing images at 40 Hz, the individual 470 nm and 410 nm signals are sampled at 20 Hz. For simultaneous GCaMP6 and R-CaMP2 imaging, camera frames were captured using alternating excitation sources of either 470 nm+560 nm or 410 nm alone. For simultaneous GCaMP6 imaging and optogenetic stimulation, camera frames were captured only with 470 nm excitation light, and additional 470 nm or 594 nm stimulation light pulses were independently controlled.

Setup for concurrent acquisition of isosbestic control. For measurements of GCaMP6 emission, both a 405 nm LED and a 470 nm LED (Thorlabs, M405F1 and M470F1) were used as excitation sources for the calcium-dependent and calcium-independent isosbestic control measurements, respectively. The two LEDs were filtered with a 410-10 nm and 470-10 nm 1″ Ø bandpass filters (Thorlabs, FB410-10 and FB470-10), fiber coupled as described above, combined using a 425 nm longpass dichroic mirror (Thorlabs, DMLP425R) and coupled into the microscope using a 495 nm longpass dichroic mirror (Semrock, FF495-Di02-25×36).

Dual-color recording setup. To enable simultaneous GCaMP6 and R-CaMP2 recording, the 535 nm bandpass emission filter was removed and an image splitter (Photometrics, DualView-Lambda®) was introduced in between the camera and the tube lens, enabling us to record the GCaMP6 and R-CaMP2 emission onto separate halves of the same camera sensor. Inside the image splitter, a 555 nm dichroic mirror (Semrock, FF555-Di03-25×36) separates the emission into two channels, each of which are additionally filtered by a 600-37 nm (Semrock, FF01-600/37-25) and 520-35 nm emission filters (Semrock, FF01-520/35-25), respectively, and then projected onto the camera sensor. An additional dichroic cube allowed us to incorporate a 565 nm LED (Thorlabs, M565F1) for R-CaMP2 excitation with a 560-14 nm excitation filter (Semrock, FF01-560/14-25), in conjunction with the 410 nm and 470 nm LEDs as described previously for GCaMP6 recording. Each of the three LEDs was coupled via a 1000 μm Ø, 0.48 NA fiber (Thorlabs) to either a 405 nm f=4.02 mm, 0.6 NA collimator (410 nm and 470 nm LED; Thorlabs, F671SMA-405 and AD11F) or a 543 nm f=4.34 NA collimator (560 nm LED; Thorlabs, F230SMA-A). The 410 nm and 470 nm output from the collimators were first combined with a 425 nm longpass dichroic mirror (Thorlabs, DMLP425R), and then combined with the 560 nm light using a second 520 nm dichroic, (Semrock, FF520-Di02-25×36), before finally being coupled into the microscope using a third multi-band dichroic (Semrock, FF410/504/582/669-Di01-25×36).

Setup for simultaneous recording and stimulation. For combined imaging and optogenetic stimulation, the 565 nm LED used for dual-color recording was replaced with a 594 nm laser (Cobolt, Mambo 100 mW). The 594 nm laser was filtered with a 590-10 nm bandpass filter (Thorlabs FB590-10). An additional 525-39 nm green fluorescent protein (GFP) emission filter (Semrock, FF01-525/39-25) was placed in front of the tube lens, along with a 594 nm notch filter (Semrock, NF03-594E-25) to minimize direct laser emission detected by the camera. A multi-band dichroic (Semrock, Di01-R405/488/594-25×36) was used to reflect 470 nm and 594 nm excitation light into the back of the 20× objective. A high-speed shutter (Stanford Research Systems, SR474) was placed in front of the laser to modulate the emission in synchrony with the other LEDs and camera.

For 470 nm cross-stimulation experiments, to enable the delivery of 470 nm excitation light at two different power levels, the 594 nm laser was replaced with another 470 nm LED, and the dichroic combining the 470 nm and 594 nm light was replaced with a 50:50 beamsplitter. During the cross-stimulation experiments, one 470 nm LED was set to a lower power and activated for every camera exposure, while the other 470 nm LED was set to a similar or higher power and activated only during the stimulation periods.

Setup for sCMOS and lock-in amplifier photoreceiver comparison. In order to precisely replicate the previous photoreceiver lock-in detection approach, an optical chopping wheel was introduced after the collimated 470 nm LED (Thorlabs, MC1510 and MC2000), and coupled it to the microscope via a 200 μm Ø, 0.39 NA fiber (Thorlabs, M75L01) and a 543 nm, f=7.86 mm, 0.51 NA collimator (Thorlabs, F240FC-A and AD12F) to illuminate only the center ˜254 μm Ø region of the 400 μm Ø patchcord (˜10 mm (objective focal length)÷7.86 mm×200 μm). This alignment was achieved by positioning the collimator using a 5-axis kinematic mount (Thorlabs, K5X1) and using the camera to visualize both the 400 μm Ø imaging patchcord, and the size of the excitation spot from the 200 μm Ø fiber-coupled LED using a fluorescent slide (Chroma, 92001) mounted at the working distance of the objective. For this experiment, the 470 nm LED was the only excitation light source used with a 470 nm 1″ Ø bandpass filter (Thorlabs, FB470-10) and a 495 nm longpass dichroic mirror (Semrock, FF495-Di02-25×36). Lastly, the signal from the optical chopping wheel was synchronized to a lock-in amplifier (Stanford Research, SR810 DSP), the output of which was sampled and digitized at 10 kHz using data acquisition hardware (National Instruments, NI PCIe-6343-X).

Image Acquisition Using MATLAB®

Though the technique described here could be implemented using the standalone image acquisition software for the sCMOS camera and digital function generators to control the light sources, custom MATLAB® software was used to control all hardware and streamline data acquisition. All software ran on a Dell T5600 computer running Windows® 7 (64-bit). A custom Matlab® graphical user interface (GUI) controlled both the sCMOS camera through the MATLAB® Image Acquisition Toolbox and the LED light sources through a data acquisition hardware (DAQ) (National Instruments, NI PCIe-6343-X) and the MATLAB® Data Acquisition ToolBox. To minimize raw data volume for real-time applications, the camera was set to 4-by-4 pixel binning and semi-automatically located a subregion containing only each of the fiber ends from which to acquire data. Using this software, the 7 fiber signals from the raw camera frame can be calculated within ˜2-3 ms (measured when collecting both calcium and isosbestic signals at 40 Hz, and given the computer's configurations). Separate scripts for each experiment generated digital control signals to operate any mouse behavior peripheral hardware. The GUI software and example behavior control scripts are available at https(colon)//github(dot)com/deisseroth-lab/multifiber.

Head-Fixed Apparatus and Stimulus Delivery

Except for during the freely moving 7-fiber recordings, mice were head-fixed above an animal running wheel (Ware, Small 6″ wheel) using a custom machined head-plate holder. Custom-written Matlab® scripts delivered digital control signals to trigger water rewards and tail shocks synchronized to the camera imaging. Water rewards were delivered through a small animal feeding tube (Popper and Sons, 16 gauge) connected to a normally-closed solenoid (Valcor, SV74P61T-1). The solenoid was powered by a 12V DC battery, and the power was gated by a metal-oxide-semiconductor field-effect transistor (MOSFET) (Mouser Electronics). The solenoid was opened for 0.25-0.5 s, which resulted in water droplets a few 10 s of μL in size. Tail shocks were administered using a stimulus isolator (WPI, Isostim A320R). The positive and negative leads of the isolator were connected by lead wires (Roscoe Medical, WW3005) to two pre-gelled electrodes (Sonic Technology) that were attached to the mouse's tail.

Analysis

All analysis was performed using custom-written scripts in MATLAB®. Regions of interest (ROIs) were first manually drawn around the fiber(s) based on a mean image of the movie. The average fluorescence intensity was calculated for each fiber. A “dark frame” image was acquired by taking a movie with the patchcord attached to the mouse, but with no LEDs on. This offset value accounts for extraneous, non-genetically-encoded calcium indicator (GECI) related light contributing to the signal. This offset was subtracted from the fluorescence intensity for each fiber, and then the fluorescence time series was thresholded to remove large transients. A double exponential was then fit to the fluorescence time series, and the best fit was subtracted in order to account for slow bleaching artifacts. A single baseline fluorescence value was calculated, either as the median of the entire trace (which robustly estimated the baseline fluorescence), or by manually defining the baseline during visually-identified periods of rest. The normalized change in fluorescence (dF/F) was calculated by subtracting the baseline fluorescence from the fiber fluorescence at each time point, and dividing this value by the baseline fluorescence. For 7-fiber experiments, the dF/F was further normalized by the maximum value for each fiber. For analysis shown in FIGS. 1C-1E, the 410 nm reference trace was scaled to best fit the 470 nm signal using least-squares regression. The scaled 410 nm reference trace was then subtracted from the 470 nm signal to obtain the motion-corrected 470 nm signal. Other than the plots shown in FIG. 1B for the 7-fiber imaging, no additional smoothing or filtering was applied to fluorescence measurements. For FIG. 1B, a 1 s average sliding window was applied to the traces. To calculate correlation coefficients, MATLAB®'S “con” function was used. To ensure that the increase in correlation during the social interactions was significantly greater than what one would expect from merely increased activity, each fiber's trace was circularly permuted 1,000 times using a random shift between 0 and 5 minutes. For each shuffle, the pooled mean r value was calculated across all mice and unique brain region pairs. A p-value <0.001 means that none of the mean r values calculated from the 1,000 shuffled traces were greater than the actual calculated mean r value.

Experimental Parameters

sCMOS and lock-in amplifier photoreceiver experiments. Mice were water deprived to ˜80% of their starting weight. Head-fixed mice were trained to lick water rewards that were delivered through an animal feeding needle. Water rewards were given as a 0.25 s opening of the solenoid, and delivered at 10 s intervals. The SNR was calculated as the peak dF/F divided by the standard deviation of the baseline dF/F. Here, the peak dF/F was the maximum value during the first 2 s of reward, and the baseline dF/F was measured during the period 0.5 s prior to reward delivery. Only a single fiber was implanted in the VTA. A low imaging power of 2.5 μW (measured at the face of a 400 μm Ø patchcord) was used. For imaging parameters, see Example 6.

Multi-fiber experiments. For the 7-fiber experiment, the branching patchcord was coupled to the ferrules implanted in the mouse with ceramic sleeves. The mouse was allowed to freely navigate its cage and socialize with a novel mouse (of the same gender and age) while calcium signals were recorded. For 7-fiber experiments, alternating frames with excitation wavelengths of 470 nm and 410 nm were imaged at 40 Hz, resulting in frame rates of 20 Hz for both the GCaMP6 calcium and isosbestic control signals. For the 4-fiber experiments, mice were water-deprived and administered either water rewards or tail shocks while head-fixed and running on a wheel. Water rewards were given as a 0.5 s opening of the solenoid, and tail shock were given as 450 ms pulses spaced 5 ms apart for 2 s (4 shocks at 0.5 Hz). Water rewards and shocks were given at 10 s intervals. The response size to reward or shock was defined as the difference between the mean stimulus dF/F during the first 1 s of the reward or shock, and the mean baseline dF/F during the 2 s prior to the reward or shock. For 4-fiber experiments, alternating pulses with excitation wavelengths of 470 nm and 410 nm were imaged at 20 Hz, resulting in frame rates of 10 Hz for both the GCaMP6 calcium and isosbestic control signals. Typically 10-20 μW of 470 nm imaging light power was used, and 410 nm LED light power was adjusted to approximately match the GCaMP6 fluorescence emission produced by the 470 nm imaging light.

Dual-color experiments. Mice were water-deprived and administered either water rewards or tail shocks while head-fixed using the same parameters as in the multi-fiber experiments. Response sizes to reward or shock were calculated as described for the multi-fiber experiments. Alternating pulses of simultaneous 470 nm and 560 nm light, and 410 nm light, were imaged at 20 Hz, resulting in frame rates of 10 Hz for GCaMP6 and R-CaMP2, and for the control signals. 10-20 μW of 470 nm and 560 nm imaging light power was used, and the 410 nm LED light power was adjusted to approximately match the GCaMP6 and R-CaMP2 fluorescence emission produced by the 470 nm and 560 nm imaging light.

Combined imaging and stimulation experiments. Mice were water-deprived and administered either optogenetic stimulation or water rewards while head-fixed using the same parameters as in the multi-fiber experiments. The response size to optogenetic stimulation or reward was defined as the difference between the mean stimulus dF/F during the first 0.5 s of the light or reward, and the mean baseline dF/F during the 0.5 s prior to the light or reward. To sample calcium signals at 20 Hz, 470 nm excitation pulses that were 12.5 ms in length and spaced 50 ms apart were used for a 25% duty cycle. The camera exposed frames only during each 470 nm excitation pulse, resulting in 25% duty cycle imaging. Additional 470 nm or 594 nm stimulation pulses were delivered in between the 470 nm imaging excitation pulses, at a rate of 20 Hz for 0.5 s (10 pulses with 12.5 ms pulse width for a 25% duty cycle). Though longer exposure times could have been used to increase the amount of signal recorded, a larger separation between the stimulation periods and the camera exposure times was chosen, so that there was no question about whether signal artifacts were being measured, where the 470 nm or 594 nm stimulation pulses contributed additional excitation of GCaMP6 within a camera exposure. A 410 nm isosbestic GCaMP control signal was not recorded for these experiments. Identical light powers for the 470 nm imaging and stimulation pulses for the 5 μW and 10 μW experiments were used. However, for the 50 μW and 220 μW 470 nm stimulation pulses, the imaging 470 nm LED was kept at 10 μW to avoid unnecessary bleaching of the GCaMP6 fluorescence, and the additional stimulation 470 nm LED was set to 50 or 220 μW. For all 594 nm stimulation pulses and water reward measurements, the imaging 470 nm LED was kept at 5 μW. For the control mouse, GCaMP6 fluorescence was recorded with 20 μW pulses of 470 nm imaging light, and identical 20 μW pulses of 470 nm stimulation light and 0.5 mW pulses of 594 nm stimulation light. GCaMP6 fluorescence with 50 μW pulses of 470 nm imaging light, and identical 50 μW pulses of 470 nm simulation light and 0.5 mW pulses of 594 nm stimulation light, were also recorded.

Cultured Neuron Intracellular Patching and Imaging for GECI Isosbestic Wavelengths

Dissociated rat hippocampal neurons were cultured and transfected with both GCaMP6m and R-CaMP2 as previously described. Coverslips of cultured neurons were transferred from the culture medium to a recording bath filled with Tyrode's solution (containing in mM: 125 NaCl, 2 KCl, 2 CaCl₂, 2 MgCl₂, 30 glucose, 25 HEPES). Whole-cell patch clamp recordings were performed on healthy GECI-expressing neurons at room temperature. Resistance of the glass patch pipettes was 3-4 MS2 (Sutter Instruments, P-2000) when filled with intracellular solution containing the following (in mM): 150 K-gluconate, 5 NaCl, 1 MgCl₂, 0.2 EGTA, 10 HEPES, 2 Mg-ATP, 0.3 Na-GTP, adjusted to pH 7.3 with KOH. Signals were amplified with a Multiclamp 700B amplifier, and acquired using a DigiData 1440A digitizer sampled at 10 kHz and filtered at 2 kHz (Molecular Devices). All electrophysiological data acquisition was performed using pCLAMP software (Molecular Devices). Imaging was performed using a 40×/0.8 NA objective (Olympus), Rolera XR camera (Q-Imaging), and Spectra X Light excitation source (Lumencor), all coupled to an Olympus BX51 WI microscope. The following bandpass filters were used with the Lumencor for excitation wavelengths: 405-10 nm (Thorlabs, FB405-10), 470-10 nm (Thorlabs, FB470-10), and 560-10 nm (Thorlabs, FB560-10). GCaMP6m emission was reflected off a 495 dichroic mirror (Semrock, FF495-Di03-25×36) and passed through a 535-30 nm emission filter (Chroma, ET535/30m), and R-CaMP2 fluorescence was reflected off a 585 nm dichroic (Chroma, T585LP) and passed through a 630-75 nm emission filter (Chroma, ET630/75m). Images were acquired at 10 Hz using QCapture Pro7 Software (Q-imaging). While synchronously measuring GCaMP6m or R-CaMP2 fluorescence from a neuron, action potentials were driven by injecting brief current pulses (5 ms, 1-2 nA) at 10 Hz for 3 s (resulting in 30 action potentials). The response size to the stimulation train was defined as the difference between the mean stimulus dF/F during the first 3 s of the stimulation train, and the mean baseline dF/F during the 3 s prior to the stimulation train.

bReaCh-ES Design and Characterization

bReaCh-ES was generated by introducing a Glu123Ser mutation in the previously published ReaChR construct (see also, Example 8). Dissociated rat hippocampal neurons were cultured and transfected with either ReaChR or bReaCh-ES. The same intracellular recording procedures were used as for the GECI isosbestic cultured neuron intracellular recordings. Action potentials were elicited with a 4 s pulse train of 590 nm light (5 ms pulse width) delivered at various frequencies, using a Spectra X Light source and 590-10 nm excitation filter (Thorlabs). Steady-state current and tau-off kinetics were measured using a constant illumination of 4 s.

Animal Surgical Procedures and Viruses

All experimental and surgical protocols were approved by Stanford University's Institutional Animal Care and Use Committee. For all surgeries, stainless steel headplates and ferrules were fixed to the skull using Metabond (Parkell). Mice were anesthetized with 1.5-2.0% isoflurane and were placed on a heating pad in a stereotaxic apparatus (Kopf Instruments). All viruses were produced at the Stanford Viral and Vector Core—GVVC (Stanford University).

For the 7-fiber surgery, DAT::Cre B6.SJL-S1c6a3tm1.1(cre)Bkmn/J (JAX® stock 006660) male or female transgenic mice were stereotaxically injected as previously described with 1000 nL of AAVDJ-CaMKIIα-GCaMP6f (2.7e12 vg/ml) at six locations: PFC, A/P +2.2, M/L +0.35, D/V −2.2; NAc, A/P +1.15, M/L −1.65, D/V −4.2; BLA, A/P −1.54, M/L −3.0, D/V −4.6; LH, A/P −0.9, A/P −1.1, D/V −5.0; BNST, A/P +0.9, M/L +0.1, D/V −4.4; and CA1, A/P −1.75, M/L +1.5, D/V −1.25. Mice were injected with 1000 nL of AAVDJ-EF1α-DIO-GCaMP6f (1.5e13 vg/ml) in the VTA: A/P −3.1, M/L −0.4, D/V −4.4. Custom 400 μm Ø 0.48 NA fibers attached to a 1.25 mm Ø stainless steel ferrule (Doric Lenses) were stereotaxically implanted at the same seven coordinates.

For 4 fiber surgeries, DAT::Cre male or female transgenic mice were used. Mice were stereotaxically injected as previously described with 1000 nL of AAVDJ-EF1α-DIO-GCaMP6f (1.5e13 vg/ml) at two locations in the VTA: A/P −3.3, M/L −0.3 and −0.5, D/V −4.2. Custom 400 μm Ø 0.48 NA fibers attached to a 1.25 mm Ø stainless steel ferrule (Doric Lenses) were stereotaxically implanted at 4 locations: VTA, A/P −3.3, M/L −0.4, D/V −4.2; PFC, A/P +2.2, M/L −0.35, D/V −2.0; NAc, A/P +1.2, M/L −1.75, D/V −4.0; and BLA, A/P −1.54, M/L −2.8, D/V −4.5.

For dual-color R-CaMP2 and GCaMP6 imaging, 1000 nL of a 1:1 mixture of AAVDJ-hSyn-DO-GCaMP6m (2.9e12 vg/ml) and AAVDJ-EF1α-DIO-RCaMP2 (8.0e12 vg/ml) was injected into the VTA at A/P −3.3, M/L −0.4, D/V −4.2. A custom 400 μm Ø 0.48NA fiber attached to a 1.25 mm Ø stainless steel ferrule was implanted at the same location.

For GCaMP6 imaging and bReaCh-ES stimulation, 1000 nL of a 1:1 mixture of AAVDJ-EF1α-DIO-GCaMP6f (1.5e13 vg/ml) and AAVDJ-EF1α-DIO-bReaCh-ES-TS-mCherry (5.8e12 vg/ml) was injected into the VTA of a DAT::Cre mouse at A/P −3.3, M/L −0.4, D/V −4.2. A custom 400 μm Ø 0.48 NA fiber attached to a 1.25 mm Ø stainless steel ferrule was implanted at the same location. As a control, a DAT::Cre mouse was injected with 1000 nL of a 1:1 mixture of AAVDJ-EF1α-DIO-GCaMP6f (5.8e12 vg/ml) and AAV8-EF1α-DIO-mCherry (1.7e13 vg/ml) into the VTA, and implanted with a 400 μm Ø 0.48 NA fiber at the same coordinates.

Histology

Mice were heavily anesthetized with isoflurane, and then perfused with 20 mL of cold phosphate buffered saline (PBS) followed by 20 mL of cold paraformaldehyde (PFA). The brain was extracted from the skull and kept in PFA for 24 hours, and then transferred to a 30% sucrose solution. After 48 hours, the brains were sliced into 50-100 μm thick sections using a vibratome (Leica VT1200S) in cold PBS. Slices were then washed in PBS at room temperature 3 times for 5 minutes each. For GCaMP6 and tyrosine hydroxylase (TH) staining, slices were incubated in a blocking solution of PBS+0.3% Triton®-X (polyethylene glycol p-(1,1,3,3-tetramethylbutyl)-phenyl ether) (PBST) with 5% normal donkey serum (NDS) for 1 hour. Slices were then incubated for 24 hours at 4° C. in PBST+NDS blocking solution containing a primary rabbit antibody against GFP conjugated to Alexa®488 (Life Technologies, A21311, 1:500) and a primary chicken antibody against TH (Ayes Lab, 1:500). Slices were washed 3 times for 10 minutes in PBST, and incubated in blocking solution containing a donkey anti-chicken Alexa® 647 secondary antibody (Millipore, AP194SA6) for 2 hours at room temperature. Slices were washed with PBST 3 times for 10 minutes each, and finally stained for (4′,6-diamidino-2-phenylindole) DAPI (1:1000) for 10 minutes and mounted onto glass slides. For the TH staining in the dual-color mouse, normal goat serum (NGS) was used instead of NDS, and no Triton®-X (polyethylene glycol p-(1,1,3,3-tetramethylbutyl)-phenyl ether) was added at any step. The same TH antibody was used with a goat anti-chicken Alexa®647 secondary antibody (Life Technologies, A21449, 1:500). No DAPI or primary antibodies against GCaMP6 or R-CaMP2 were used.

Example 2 System Design, Alignment, and Calibration Considerations for FIP Microscopy

A basic microscope consisting of the objective lens and tube lens was constructed, where the sCMOS camera was focused on the fiber(s) mounted at the working distance of the objective (FIG. 1A). Here, the objective and tube lens were chosen to set the magnification of the fibers onto the sensor, which determines the number of pixels on the camera that a given fiber tip is imaged onto. Note that the objective field of view and NA is larger than the fiber size and NA. Given that the dominant noise source of the sCMOS camera is read noise, the image may be sampled with as few sCMOS pixels as possible without saturating any pixels. However, for low light levels, photon shot noise may dominate the read noise, in which case more excitation light power may be used to generate more emission photons, and more camera pixels may be used to sample the emission without saturating. The excitation light sources were then added using dichroic mirrors between the tube lens and the objective. Similar to the tube lens of the camera, the focal length of the collimators for each excitation light source was chosen to set the magnification and NA to correctly fill the fiber(s). To align the relayed image of each excitation light source onto the previously aligned fiber(s), the position of the fiber(s) was annotated in the camera view and the excitation light sources were each positioned to be centered over the fiber(s) (FIG. 3A). Finally, in the dual-color imaging experiments with the image splitter, the image splitter was simply attached to the camera and positioned until the now two images of the fiber(s) were in focus again. The synchronization of the light sources to the sCMOS camera was tested using a fluorescent slide. The duty cycle and precise on-time of each light source was adjusted to accommodate the camera's rolling shutter and the off-slew-rate of each light source. This timing adjustment can be done once for each light source for each set of digital control waveforms.

Example 3 Simultaneous Calcium Measurements from Multiple Deep Brain Regions Using an sCMOS Camera

To develop FIP microscopy, in vivo GCaMP6 recordings obtained with an sCMOS camera was compared to those obtained with a previously published design involving a photoreceiver and lock-in amplifier. The camera setup was modified to direct half the fluorescence emission from a single fiber onto a photoreceiver using a beamsplitter; excitation light was modulated for lock-in detection as previously described. The sCMOS camera measurement (even without lock-in detection) was found to be at least as sensitive as the measurement using a photoreceiver and lock-in amplifier (see Example 6; FIGS. 3A-3C).

The beamsplitter and photoreceiver was then removed to collect all fiber emissions onto the camera sensor. To control for non-Ca²⁺ related fluorescence changes due to brain motion or fiber bending, camera frames corresponding to excitation of GCaMP6 and R-CaMP2 near their respective optical Ca²⁺-dependent excitation wavelengths (470 nm or 560 nm), and also near the isosbestic wavelength (410 nm) were alternately acquired. Using simultaneous imaging paired with intracellular current injection-driven defined spiking patterns in cultured neurons, it was confirmed that GCaMP6 and R-CaMP2 increased fluorescence emission in response to action potentials when excited at 470 nm and 560 nm respectively, but exhibited virtually no change in emitted fluorescence when excited near 410 nm (see Example 7; FIGS. 4A-4F). Thus any changes observed while imaging either GCaMP6 or R-CaMP2 with 410 nm light were likely due to either motion-related artifacts or changes in intrinsic signals unrelated to neural activity. The ability to simultaneously record both the calcium-dependent signal and the 410 nm control signal allowed identification of artifacts that contaminate the signal in real-time, rather than in separate fluorophore-only cohorts. It was confirmed that large motion artifacts could be detected and corrected for in vivo when imaging GCaMP6 simultaneously with 470 nm and 410 nm light (FIG. 5).

FIG. 5. Example of correcting motion-related artifacts present in the 410 nm isosbestic wavelength. Example of simultaneously recorded GCaMP6 signals using 470 nm and 410 nm excitation (left traces). The 410 nm signal has been scaled using least-squares regression to minimize the difference between the 410 and 470 nm signal. The scaled 410 nm trace from the 470 nm trace was then subtracted to generate the corrected 470 nm signal (right trace).

The FIP microscope's ability to simultaneously record GCaMP6 Ca²⁺ signals from multiple fibers in vivo was then tested. A 7-fiber patchcord tightly bundled on one end and split into 7 separate branches on the other was used, to both deliver excitation light and collect emission light. Each of these 7 branches was coupled to a fiberoptic interface implanted into different widely-dispersed regions in an adult mouse; a single fast sCMOS camera then was interfaced to the output end, simultaneously measuring fluorescence emission from all 7 fibers by imaging the tightly bundled end of the patchcord (FIG. 1A). Using the FIP microscope, simultaneous and temporally registered GCaMP6f signals across the brain in a freely moving mouse was then measured. The targeted areas were 1) bed nucleus of the stria terminalis (BNST), 2) nucleus accumbens (NAc), 3) ventral tegmental area (VTA), 4) lateral hypothalamus (LH), 5) basolateral amygdala (BLA), 6) hippocampal region CA1, and 7) prefrontal cortex (PFC) in DAT::Cre driver mice. A Cre-dependent GCaMP6f virus was injected into the VTA to preferentially label dopamine (DA) neurons, while a CaMKIIα-GCaMP6f virus was injected in the other regions. GCaMP6f fluorescence signals that were present with 470 nm excitation, but absent with isosbestic-range 410 nm excitation (FIG. 1B) where only small, non-Ca²⁺ dependent changes (likely due to motion or system-related artifacts; for example in CA1) were observed. The 470 nm signals were then normalized by the 410 nm control traces, and neural activity was measured across all 7 brain regions during naturalistic and freely-moving social interactions. Spontaneous activity could be robustly observed in all 7 brain regions, in addition to a time-locked increase in fluorescence activity upon the introduction of a novel mouse (FIG. 1C). Joint-statistical relationship among the brain regions was calculated using Pearson's correlation during periods when the mouse was alone versus when the mouse was socializing (FIG. 1D), and a global increase in pair-wise correlations across brain regions was observed when the mouse was socializing with a novel mouse (FIG. 1D). Shuffling analysis confirmed that this increase in pair-wise correlations was significantly greater than what would expected from simply increased activity in all of these regions (p<0.001, out of 1,000 shuffles).

FIG. 1. Simultaneous calcium measurements from multiple deep brain regions using an sCMOS camera. FIG. 1A) Schematic of microscope for simultaneous FIP calcium recordings. An example image of the bundled fiber faces is shown in the upper right inset. The lower left inset illustrates the time-division multiplexing scheme for simultaneously imaging GCaMP6 with 470 nm and 410 nm. FIG. 1B) Left: example image of a mouse implanted with 400 μm fibers in 7 different regions expressing GCaMP6f. Center: example calcium traces recorded from a freely moving mouse. Right: simultaneously recorded control traces. FIG. 1C) Example GCaMP6f fluorescence traces simultaneously acquired across the 7 different brain regions listed in FIG. 1B) when the mouse was alone versus when the mouse was placed with a novel mouse. The total imaging time was 10 min for each condition. Traces are plotted as dF/F normalized to each trace's maximum value. FIG. 1D) Top: Heat maps of the Pearson's correlation coefficients (r) calculated between all 7 brain regions for the example mouse shown in FIG. 1C). Bottom: Spatial representations of the Pearson's correlation coefficients between each brain region. Brain regions are plotted according to the anterior/posterior and medial/lateral coordinates where the fibers were implanted. The thickness of the lines connecting each brain region represents the magnitude of r. FIG. 1E) Summary of the mean r values between all brain regions calculated when the mouse was alone versus in the presence of a novel mouse. The mean r value significantly increased in the presence of a novel mouse compared to the baseline alone value (0.31±0.024 versus 0.43±0.024, p<0.001, n=84 pairs from 4 mice, Wilcoxon's rank-sum test). FIG. 1F) Schematic of surgery and recording setup for 4-fiber experiment. FIG. 1G) Example GCaMP6f fluorescence traces simultaneously acquired in each brain region in response to reward and tail shock. Solid lines denote calcium transients, dashed lines denote control signal (mean±S.E.M.; n=6 trials from one mouse). FIG. 1H) Summary of the mean responses to reward and shock in each brain region (dF/F_(stimulus)−dF/F_(baseline)). Asterisks indicate significant response (p<0.05, n=6 trials, Wilcoxon's signed-rank test).

The sensitivity limits of the system were next tested by recording Ca²⁺ signals not only from populations of cell bodies, but also from axonal projections to multiple independent regions. Here, a single injection of Cre-dependent GCaMP6f was made into the VTA of DAT::Cre driver mice. Optical fibers were then implanted in PFC, NAc, BLA, and VTA to simultaneously record from VTA-DA cell bodies or their axonal terminals in these downstream regions with the FIP microscope while administering controlled, time-locked water rewards or aversive tail shocks (FIG. 1F). It was found that the VTA-DA cell bodies exhibited increased activity during the rewarding stimulus, and decreased activity in response to the aversive tail shock, consistent with previous recordings from VTA-DA neurons. In contrast, the VTA-DA→BLA projection increased activity in response to both the reward and the tail shock. The VTA-DA→NAc projection showed a similar pattern compared with the VTA-DA cell bodies (increased activity in response to reward and decreased in response to tail shock), but activity in the VTA-DA→PFC projection exhibited yet a third pattern (increased response to tail shock but not reward; FIG. 1G, solid dark green). Supporting validity of the FIP approach, these results were consistent with previous studies that individually and separately tracked activity in different populations of VTA-DA neurons encoding rewarding or aversive stimuli depending on their projection target (though without the joint simultaneity of FIP during behavior).

Response sizes are summarized in FIG. 1H; as expected, there was little change in the GCaMP6f control signal measured at 410 nm (FIG. 1G, dashed light green). Raw GCaMP6f fluorescence traces are shown in FIGS. 6A-6B, and mean changes for the control signals are plotted in FIG. 6C (all insignificant). Table 1 summarizes the significant GCaMP6f responses recorded during reward and shock (with insignificant changes in GCaMP6f isosbestic control fluorescence). Histology confirming locations of fibers and expression of GCaMP6f in cell bodies and terminals is provided in FIGS. 7A-7D. Note that very sparse GCaMP6f fibers localized to the amygdala regions surrounding the BLA was observed, and these fibers could also be contributing to the signal.

TABLE 1 Number of mice showing significant GCaMP responses to reward or tail shock with 470 nm light for 4-fiber experiment. Brain Region Reward Tail Shock VTA-DA in PFC N.S. 3 mice VTA-DA in NAc 7 mice 4 mice VTA-DA in BLA 3 mice 2 mice VTA-DA 6 mice 5 mice p < 0.05, Wilcoxon's signed-rank test, n = 6-12 trials for each mouse. p > 0.05 for control GCaMP6 responses with 410 nm light for all mice.

Example 4 Dual Color Imaging of Different Populations

The FIP microscope was readily adaptable for dual-color imaging of different populations using two different Ca²⁺ sensors (in this case GCaMP6 and R-CaMP2). By placing an image splitter in front of the camera sensor and adding an additional 560 nm excitation source (FIG. 8A), it was possible to simultaneously collect GCaMP6 and R-CaMP2 fluorescence emission through the same fiber. VTA-DA expressing and VTA-non-DA expressing neurons in DAT::Cre mice was labeled using a Cre-activated (DIO) AAV:R-CaMP2 virus and a Cre-deactivated (DO) GCaMP6m virus, respectively (FIG. 2A). This viral strategy resulted in labeling of largely non-overlapping populations of R-CaMP2 and GCaMP6m neurons in the VTA (FIG. 2B), and expression of DIO:R-CaMP2 was found to co-localize with the tyrosine hydroxylase (TH) stain for DA-expressing neurons (FIGS. 9A-9B). While monitoring these neural populations with the FIP microscope, reward or tail shock stimuli was administered. Consistent with the earlier 4-fiber recordings, it was found that activity in VTA-DA neurons significantly increased in response to reward and significantly decreased in response to tail shock (FIG. 2C-2D). It was found that the VTA non-DA neurons exhibited a significant increase in fluorescence in response to both reward and tail shock (FIG. 2C-2D), consistent with previous electrical recordings. There was no significant change in R-CaMP2 or GCaMP6m control fluorescence in response to 410 nm excitation during reward or tail shock (FIG. 2C).

FIGS. 2A-2D. Dual-color imaging of different populations. FIG. 2A) Schematic of dual-color imaging surgery preparation. FIG. 2B) Non-overlapping populations of VTA-DA neurons and VTA-non-DA labeled with R-CaMP2 and GCaMP6m, respectively. Scale bar indicates 25 μm. FIG. 2C) VTA-DA and VTA-non-DA fluorescence traces in response to reward and tail shock (red, VTA-DA neurons; green, VTA-non-DA neurons; solid curves, calcium transients; dashed curves, control signals). FIG. 2D) Summary of the mean responses to reward and shock (dF/F_(stimulus)−dF/F_(baseline)). VTA-DA neural activity increased in response to reward (5.39±0.32% dF/F) and decreased in response to shock (−1.18±0.45% dF/F), while VTA-non-DA neural activity increased in response to both reward (3.26±0.14% dF/F) and shock (2.08±0.14% dF/F). Asterisks indicate p<0.05, n=10 trials, Wilcoxon's signed-rank test.

FIG. 8A. Microscope configuration used for dual-color imaging experiments. a) Schematic of setup for dual-color imaging. An image splitter was placed before the camera sensor, and an additional 560 nm LED was used to image R-CaMP2. The lower left inset represents the time-division multiplexing strategy used to simultaneously image GCaMP6 and R-CaMP2 at both their calcium sensitive and insensitive wavelengths.

FIGS. 7A-7B. Confirmation of fiber location and virus specificity for dual-color imaging. FIG. 7A) 10× magnification images of a slice containing VTA. GCaMP6m fluorescence in VTA-non-DA neurons is shown in green, R-CaMP2 fluorescence in VTA-DA neurons is shown in red, and a TH stain is shown in white. Dashed white rectangle indicates fiber location. Scale bar indicates 100 μm. FIG. 7B) 63× magnification images of VTA slice with same staining. Bottom right image is a merge of all three channels. Scale bar indicates 25 μm.

Example 5 Dual Color Imaging of Different Populations

The FIP microscope readily allowed tuning optogenetic stimulation to match activity levels that naturally occurred with behaviorally-relevant timing within the very same targeted neural population at the same location in the same experimental subject (FIGS. 2E-2H). Simultaneous recording and perturbation of neural activity was performed using GCaMP6 and a potent and fast red-shifted channelrhodopsin, bReaCh-ES (Methods, Example 8, and FIGS. 10A-10F). The 560 nm LED used to image R-CaMP2 was replaced with a 594 nm laser for bReaCh-ES (FIG. 8B), and DIO-bReaCh-ES-TS-mCherry was virally expressed along with DIO-GCaMP6f in the VTA of DAT::Cre mice in order to both image and perturb VTA-DA neurons (FIG. 2E), anticipating that the high light sensitivity of the FIP microscope could allow recording of GCaMP6f signals under very low imaging power that would minimize cross-stimulation of bReaCh-ES by GCaMP6f excitation light (Example 9). GCaMP6f fluorescence responses to interleaved pulses of 470 nm stimulation light identical to the 470 nm pulses used to image GCaMP6 was measured; GCaMP6f responses to 594 nm pulses, and to a naturalistic water reward were also measured (FIG. 2F). It was found that using 5 μW of power (measured at the face of the 400 μm Ø patchcord, for 470 nm imaging and stimulation) resulted in minimal changes in GCaMP6f fluorescence (FIG. 2G), while higher light powers of 470 nm light elicited much larger GCaMP6f transients as a result of opsin cross-stimulation (FIGS. 11A-11B). Using only 5 μW of 470 nm imaging light power was still sufficient to observe VTA-DA responses to 594 nm bReaCh-ES stimulation that scaled with light intensity (FIG. 2G), and could be tuned to match amplitude of VTA-DA responses to water reward in the very same animal (FIG. 2G). A summary of the mean GCaMP6f response size to various stimulation wavelengths and powers is shown in FIG. 2H. A control DAT::Cre mouse expressing DIO-GCaMP6f and DIO-mCherry exhibited no significant changes in GCaMP6f fluorescence in response to interleaved 470 nm or 594 nm stimulation light, but did exhibit GCaMP6f transients as expected during interaction with a novel mouse, known to elicit VTA-DA activity (FIGS. 11C-11D).

FIGS. 2E-2H. Simultaneous recording and perturbation of neural activity. FIG. 2E) Schematic of combined imaging and optogenetics surgery preparation. FIG. 2F) Schematic of imaging paradigm. For experiments, 10 stimulation pulses were used. FIG. 2G) Example GCaMP6f fluorescence traces in response to bReaCh-ES cross-stimulation with with 5 μW of 470 nm light (light blue), bReaCh-ES stimulation with 594 nm light (light to dark orange denote 0.5 mW, 1 mW, and 2 mW of power), or a water reward (cyan). FIG. 2H) Summary of the mean responses to bReaCh-ES stimulation or reward (dF/F_(stimulus)−dF/F_(baseline)). The mean VTA-DA neuron response size to 5 μW 470 nm stimulation (n=6 trials, 2.27±0.57% dF/F) was significantly smaller than the response size to the reward (n=4 trials, 8.27±1.63% dF/F, p<0.05, Wilcoxon's rank-sum test).

FIG. 8B. Microscope configurations used for simultaneous imaging and perturbation experiments. b) Schematic of setup for simultaneous imaging and perturbation experiments. The 560 nm LED was replaced with a 594 nm laser for optogenetic stimulation. For cross-stimulation measurements, the 594 nm laser was replaced with an additional 470 nm LED, and the dichroic combining the 470 nm and 594 nm light was replaced with a 50:50 beamsplitter.

FIGS. 10A-10F. Characterization of novel bReaCh-ES opsin. FIG. 10A) Example of internal current elicited by a 4 s pulse of 590 nm light (orange) for neurons expressing ReaChR or bReaCh-ES. FIG. 10B) Voltage recordings showing 4 APs in response to 4, 5 ms pulses of 590 nm (orange) light delivered at 1 Hz to neurons expressing ReaChR or bReaCh-ES. FIG. 10C) Voltage recordings showing APs in response to 80, 5 ms pulses of 590 nm light (orange) delivered at 20 Hz to neurons expressing ReaChR or bReaCh-ES. FIG. 10D) Average tau-off kinetics measured for ReaChR and bReaCh-ES. The mean tau-off for bReaCh-ES was significantly smaller than that of ReaChR (ReaChR: 531.83±40.29 ms; bReaCh-ES: 39.33±3.69 ms; p<0.005, n=6 cells, Wilcoxon's rank-sum test). FIG. 10E) Steady-state current measured for ReaChR and bReaCh-ES. There was no significant difference between steady-state current between ReaChR and bReaCh-ES (ReaChR: 946.00±121.97 pA; bReaCh-ES: 941.17±169.30 pA; p>0.05, n=6 cells, Wilcoxon's rank-sum test). FIG. 10F) Percentage of APs successfully elicited by a 4 s train of 590 nm light pulses (5 ms pulse width) delivered at 1, 2, 5, 10, and 20 Hz to neurons expressing ReaChR or bReaCh-ES. At 10 and 20 Hz, bReaCh-ES stimulation elicits a significantly higher percentage of successful APs than ReaChR (ReaChR: 12.08±9.58% at 10 Hz, 2.29±1.04% at 20 Hz; bReaCh-ES: 100±0% at 10 and 20 Hz; p<0.005, n=6 cells, Wilcoxon's rank-sum test).

FIGS. 11A-11D. Control for simultaneous imaging and perturbation experiment. FIG. 11A) Example GCaMP6f fluorescence traces in response to bReaCh-ES cross-stimulation with 470 nm light (light to dark blue represents 10 μW, 50 μW, and 220 μW of power). FIG. 11B) Summary of the mean GCaMP6f responses to bReaCh-ES cross-stimulation with 470 nm light (dF/F_(stimulus)−dF/F_(baseline)). FIG. 11C) Top: Example GCaMP6f fluorescence trace taken from a control mouse expressing mCherry instead of bReaCh-ES to demonstrate that there is functional GCaMP6f present. Bottom: GCaMP6f fluorescence traces in response to 0.5 mW 594 nm stimulation pulses (orange), and to 20 or 50 μW 470 nm stimulation pulses (blue). FIG. 11D) Summary of the mean GCaMP6f responses to light (dF/F_(stimulus)−dF/F_(baseline)) in the mCherry control mouse. There were no significant changes in GCaMP6f fluorescence with 470 nm or 594 nm stimulation light (p>0.05 Wilcoxon's signed-rank test).

Example 6 Simultaneous Camera and Photoreceiver Lockin-In Measurements

To get a conservative estimate of how the sensitivity of the sCMOS camera without lock-in detection compares with the previous state-of-the-art technique employing lock-in detection, an experiment was conducted where the same calcium-dependent fluorescence was recorded simultaneously with both techniques. To accomplish this, the excitation light source was modulated at 448 Hz and synchronized with the lock-in amplifier configured with a −3 dB filter with 24 dB slope at 16 Hz (corresponding to 10 ms time constant), consistent with the imaging parameters described previously. Modulating the excitation source at 448 Hz minimized both the presence of 60 Hz electrical noise in the photoreceiver, and beating artifacts from the modulated light in the camera. The emission from the fiber was equally split with a beamsplitter between the photoreceiver connected to the lock-in amplifier and the sCMOS camera. In order to match the 16 Hz bandwidth detection of the lock-in amplifier, the camera was set to acquire frames at 32 Hz (to Nyquist sample the desired 16 Hz bandwidth). Importantly, while the signal from the lock-in amplifier benefits from the demodulation of the 448 Hz carrier signal, no attempt was made to demodulate the signal recorded by the sCMOS camera though it would be possible if sampling was done at a higher frame rate. Hence, the signal from the sCMOS camera was a conservative estimate of what would be measured with constant excitation without any modulation or lock-in detection.

Example 7 Isosbestic Excitation Wavelength of GCaMP6 and R-CaMP2

The published absorption spectrum of GCaMP3 and R-CaMP2 suggested that an isosbestic point between 405-420 nm exists where the absolute GCaMP or R-CaMP emission is independent of calcium concentration. Previous studies using the AM esterase dye Fura-2, for example, have used fluorescence emission collected with the isosbestic excitation wavelength to measure calcium-independent changes in fluorescence of the indicator. Thus by simultaneously measuring the GCaMP6 and R-CaMP2 fluorescence using the ˜isosbestic 410 nm wavelength, a reference signal could be recorded that reported non-calcium related fluorescence changes that could be contributing to the measured calcium signals. While both the calcium signals and control signals were presented in the Examples, one could normalize the calcium signal by its corresponding control signal to estimate neural activity-related changes in fluorescence.

Example 8 Generation of bReaCh-ES Construct

Recently a red-shifted excitatory opsin, ReaChR, was published that exhibits large photocurrents capable of transcranial optogenetic stimulation. However, photocurrents expressing ReaChR were accompanied by a long tau-off, which hindered the ability to elicit APs at frequencies higher than 1 Hz. A mutation to the existing ReaChR was introduced to generate bReaCh-ES, which exhibited the same large photocurrents as ReaChR, but had a significantly short tau-off that allows APs to be driven 100% reliably at up to 20 Hz (FIGS. 10A-10F).

Example 9 Procedure for Estimating Cross-Stimulation of bReaCh-ES

It is well known that the excitation spectrum of GCaMP6 and the excitation spectrum of red-shifted indicators such as C1V1 exhibit significant overlap. As a result, a given choice of excitation wavelength for GCaMP6 may result in unwanted bReaCh-ES cross-stimulation to some extent, and this effect may be quantified. To characterize the amount of cross-stimulation of bReaCh-ES produced by the GCaMP6 excitation light, additional pulses of 470 nm stimulation light at 20 Hz (10 pulses with 12.5 ms pulse width) were applied while imaging GCaMP6 with 470 nm light (20 Hz, 12.5 ms pulse width). As expected, with higher powers of the 470 nm blue excitation, larger changes in GCaMP6 fluorescence were observed likely due to cross-stimulation of bReaCh-ES. As a comparison, the change in GCaMP6 fluorescence was also measured to interleaved pulse trains of 594 nm light at 20 Hz (10 pulses with 12.5 ms pulse width) intended to stimulate bReaCh-ES, and to a water reward. This protocol for characterizing the amount of cross-stimulation was a more explicit measure than those used in previous papers.

While the present disclosure has been described with reference to the specific embodiments thereof, it should be understood by those skilled in the art that various changes may be made and equivalents may be substituted without departing from the true spirit and scope of the present disclosure. In addition, many modifications may be made to adapt a particular situation, material, composition of matter, process, process step or steps, to the objective, spirit and scope of the present disclosure. All such modifications are intended to be within the scope of the claims appended hereto. 

1. A method comprising: a) illuminating one or more regions of a target tissue with a light stimulus comprising light pulses of a plurality of wavelengths, wherein: each of the one or more regions is labeled with one or more cellular activity-dependent fluorescent moieties; and the light pulses comprise: i) a first set of light pulses at a first wavelength; and ii) a second set light pulses at one or more wavelengths, wherein each of the one or more wavelengths are different from the first wavelength and are at an excitation wavelength of the one or more cellular activity-dependent fluorescent moieties, and wherein each light pulse of the first set are interleaved among light pulses of the second set, thereby generating fluorescence from each of the one or more regions, wherein a multimode optical fiber is configured to direct the light stimulus to, and collect the fluorescence from, each of the one or more regions; b) recording, onto independent frames of an image detector for each light pulse, an image of a terminal cross-section of the multimode optical fiber from each of the one or more regions, wherein a cross-sectional average of the fluorescence generated in response to the second set of light pulses is representative of an aggregate cellular activity of each of the one or more regions; and c) analyzing the recorded image, to generate an output comprising a measure of the aggregate cellular activity in each of the one or more regions.
 2. The method according to claim 1, wherein the multimode optical fiber has a diameter in the range of 100 to 1000 μm and the image detector comprises an image sensor.
 3. The method according to claim 1, wherein each of the one or more regions comprises one or more collections of a plurality of neurons, or a subcellular portion thereof labeled with one or more neural activity-dependent fluorescent moieties and the one or more collections comprise one or more functionally-defined collections of a plurality of neurons.
 4. The method according to claim 3, wherein the one or more regions comprise: a first collection of a plurality of neurons, each neuron of the first collection comprising a first neural activity-dependent fluorescent moiety; and a second collection of a plurality of neurons, each neuron of the second collection comprising a second neural activity-dependent fluorescent moiety, and wherein the second set of light pulses comprise: a third set of light pulses at a second wavelength, different from the first wavelength, wherein the second wavelength is at an excitation wavelength of the first neural activity-dependent fluorescent moiety; and a fourth set of light pulses at a third wavelength, different from the first and second wavelengths, wherein the third wavelength is at an excitation wavelength of the second neural activity-dependent fluorescent moiety, and wherein the recording comprises recording a first image and a second image of the terminal cross-section of the multimode optical fiber from each of the one or more regions, wherein a cross-sectional average of the fluorescence generated in response to the third set of light pulses in the first image is representative of an aggregate neural activity of the first collection of a plurality of neurons, and a cross-sectional average of the fluorescence generated in response to the fourth set of light pulses in the second image is representative of an aggregate neural activity of the second collection of a plurality of neurons.
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 9. The method according to claim 1, wherein the analyzing comprises: 1) demarcating the cross-section of the multimode optical fiber from each of the one or more regions in the recorded image; and 2) calculating an average of the fluorescence across each of the cross-sections.
 10. The method according to claim 1, wherein the analyzing comprises 3) calculating a normalized change in the fluorescence over a baseline fluorescence for each cross-section of the multimode optical fibers in the recorded image.
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 13. The method according to claim 12, wherein the first wavelength is at an isosbestic point of at least one of the one or more cellular activity-dependent fluorescent moieties.
 14. The method according to claim 12, wherein the analyzing comprises 4) subtracting an average of the cellular activity-independent fluorescence across a cross-section from an average of the cellular activity-dependent fluorescence across the cross-section, to obtain a motion-corrected measure of the aggregate cellular activity.
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 36. The method according to claim 1, wherein the one or more cellular activity-dependent fluorescent moieties comprise a calcium- and/or a voltage-sensitive indicator dye.
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 41. The method according to claim 1, wherein the image detector is a charge-coupled device (CCD) or a complementary metal oxide semiconductor (CMOS) camera.
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 44. A system comprising: a) an illumination unit; b) an objective, wherein the objective is configured to receive light from the illumination unit and to focus the light at a working distance from the objective; c) a plurality of light conduits, each light conduit comprising one or more multimode optical fibers and defining a first end, a second end opposite the first, and a light conduit numerical aperture, wherein a terminus at the first end of each of the light conduits is at the working distance from the objective; a terminal cross-section of a multimode optical fiber at the first end of each of the light conduits is in a field of view of the objective; and the light conduit numerical aperture is less than a numerical aperture of the objective; and d) an image detector; wherein the system is configured to: generate a light stimulus comprising light pulses of a plurality of wavelengths; illuminate a region in a target tissue at the second end of each of the plurality of light conduits, wherein the region, is labeled with one or more cellular activity-dependent fluorescent moieties, wherein the plurality of wavelengths comprises one or more wavelengths at an excitation wavelength of the one or more cellular activity-dependent fluorescent moieties; collect fluorescence from the region at the second end of the same light conduit of the plurality of light conduits used to illuminate the region; and record an image comprising all of the terminal cross-sections of the multimode optical fibers at the first end of the light conduits onto a frame of the image detector.
 45. The system of claim 44, wherein the one or more multimode optical fibers have a diameter in the range of 100 to 1000 μm and the image detector comprises an image sensor.
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 48. The system of claim 44, wherein each of the light conduits comprises: an implantable fiber-optic element comprising an attachment element; and one or more multimode optical fibers configured to attach to the attachment element.
 49. The system of claim 44, wherein the plurality of wavelengths comprises a wavelength at an isosbestic point of the one or more cellular activity-dependent fluorescent moieties.
 50. The system of claim 44, wherein the plurality of wavelengths comprises a plurality of wavelengths at an excitation wavelength of a plurality of cellular activity-dependent fluorescent moieties.
 51. The system of claim 44, wherein the plurality of wavelengths comprises one or more wavelengths at an activation wavelength of one or more light-activated polypeptides.
 52. The system of claim 44, wherein the illumination unit is a light-emitting diode (LED) or an LED array or a laser.
 53. The system of claim 44, wherein the image detector is a charge-coupled device (CCD) or a complementary metal oxide semiconductor (CMOS) camera.
 54. The system of claim 44, wherein the system further comprises an image splitter.
 55. The system of claim 44, wherein the system further comprises: e) a processor; and f) a computer-readable medium comprising instructions that, when executed by the processor, causes the system to: generate a light stimulus comprising i) a first set of light pulses at a first wavelength; and ii) a second set of light pulses at one or more wavelengths, each of the one or more wavelengths different from the first wavelength, using the illumination unit, wherein the one or more wavelengths are each at the excitation wavelength of the one or more cellular activity-dependent fluorescent moieties, and wherein each light pulse of the first set are interleaved among light pulses of the second set, thereby generate fluorescence from each of the one or more regions; and record the image onto independent frames of the image detector per each light pulse.
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 57. The method according to claim 1, wherein the fluorescence emitted from each of the one or more regions is split using an image splitter to form and record a separate image for the fluorescence emitted by each of the one or more cellular activity-dependent fluorescent moieties.
 58. The method according to claim 1, wherein the plurality of wavelengths comprise wavelengths of 440 nm to 620 nm.
 59. The method according to claim 2, wherein the multimode optical fiber has a diameter of 400 μm.
 60. The method according to claim 13, wherein the isosbestic point is between 405 nm to 420 nm.
 61. The system of claim 44, wherein the region comprises one or more collections of a plurality of neurons, or a subcellular portion thereof labeled with one or more neural activity-dependent fluorescent moieties and the one or more collections comprise one or more functionally-defined collections of a plurality of neurons.
 62. The system of claim 44, wherein the objective is a microscope objective.
 63. The system of claim 44, wherein the plurality of wavelengths comprise wavelengths of 440 nm to 620 nm.
 64. The system of claim 45, wherein the multimode optical fiber has a diameter of 400 μm.
 65. The system of claim 49, wherein the isosbestic point is between 405 nm to 420 nm.
 66. The system of claim 54, wherein the system is configured to: split the fluorescence emitted from the region using an image splitter to form a separate image for the fluorescence emitted by each of the one or more cellular activity-dependent fluorescent moieties; collect fluorescence from the region at the second end of the same light conduit of the plurality of light conduits used to illuminate the region; and record a separate image for the fluorescence emitted by each of the one or more cellular activity-dependent fluorescent moieties comprising all of the terminal cross-sections of the multimode optical fibers at the first end of the light conduits onto a frame of the image detector. 